U.S. patent number 11,413,805 [Application Number 17/483,982] was granted by the patent office on 2022-08-16 for bioprinter for the fabrication of tissue.
This patent grant is currently assigned to Organovo, Inc.. The grantee listed for this patent is ORGANOVO, INC.. Invention is credited to Larry Bauwens, Scott Dorfman, Richard Jin Law, Chris Leigh-Lancaster, Tim McDonald, Keith Murphy, Nathan Smith, Ian Sohn.
United States Patent |
11,413,805 |
Murphy , et al. |
August 16, 2022 |
Bioprinter for the fabrication of tissue
Abstract
Described herein are bioprinters comprising: one or more printer
heads, wherein a printer head comprises a means for receiving and
holding at least one cartridge, and wherein said cartridge
comprises contents selected from one or more of: bio-ink and
support material; a means for calibrating the position of at least
one cartridge; and a means for dispensing the contents of at least
one cartridge. Further described herein are methods for fabricating
a tissue construct, comprising: a computer module receiving input
of a visual representation of a desired tissue construct; a
computer module generating a series of commands, wherein the
commands are based on the visual representation and are readable by
a bioprinter; a computer module providing the series of commands to
a bioprinter; and the bioprinter depositing bio-ink and support
material according to the commands to form a construct with a
defined geometry.
Inventors: |
Murphy; Keith (Palos Verdes
Estates, CA), Dorfman; Scott (Baltimore, MD), Smith;
Nathan (Ferntree Gully, AU), Bauwens; Larry
(Lilydale, AU), Sohn; Ian (Glen Iris, AU),
McDonald; Tim (Mount Waverly, AU), Leigh-Lancaster;
Chris (Murrumbeena, AU), Law; Richard Jin
(Stamford, CT) |
Applicant: |
Name |
City |
State |
Country |
Type |
ORGANOVO, INC. |
San Diego |
CA |
US |
|
|
Assignee: |
Organovo, Inc. (San Diego,
CA)
|
Family
ID: |
1000006497307 |
Appl.
No.: |
17/483,982 |
Filed: |
September 24, 2021 |
Prior Publication Data
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|
|
Document
Identifier |
Publication Date |
|
US 20220009158 A1 |
Jan 13, 2022 |
|
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
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17201892 |
Mar 15, 2021 |
|
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15816640 |
Apr 6, 2021 |
10967560 |
|
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14950567 |
Jan 2, 2018 |
9855369 |
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14530499 |
Jan 5, 2016 |
9227339 |
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13968313 |
Jan 13, 2015 |
8931880 |
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13246428 |
Oct 6, 2015 |
9149952 |
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61405582 |
Oct 21, 2010 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
C12M
21/08 (20130101); B41J 2/04553 (20130101); B41J
2/04501 (20130101); C12M 33/00 (20130101); B29C
64/106 (20170801); B41J 2/04526 (20130101); B41J
2/17503 (20130101); B41J 3/407 (20130101); B01L
3/0268 (20130101); B41J 2/04503 (20130101); B29C
64/386 (20170801); B41J 2/04563 (20130101); B29C
64/295 (20170801); B28B 1/001 (20130101); B29C
64/20 (20170801); C12N 5/0062 (20130101); B33Y
30/00 (20141201); B29C 64/209 (20170801); B29C
64/393 (20170801); B33Y 70/00 (20141201); B33Y
50/02 (20141201) |
Current International
Class: |
B33Y
50/00 (20150101); B41J 3/407 (20060101); B29C
64/20 (20170101); C12N 5/00 (20060101); B29C
64/295 (20170101); C12M 1/26 (20060101); C12M
3/00 (20060101); B29C 64/106 (20170101); B41J
2/045 (20060101); B01L 3/02 (20060101); B33Y
30/00 (20150101); B28B 1/00 (20060101); B29C
64/393 (20170101); B29C 64/386 (20170101); B41J
2/175 (20060101); B29C 64/209 (20170101); B33Y
70/00 (20200101); B33Y 50/02 (20150101) |
Field of
Search: |
;425/90,96,135,145,375
;347/5,17,19,20,44,47,86,100 ;435/283.1,289.1 |
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|
Primary Examiner: Tentoni; Leo B
Attorney, Agent or Firm: Sterne, Kessler, Goldstein &
Fox P.L.L.C.
Parent Case Text
REFERENCE TO RELATED APPLICATIONS
This application is a continuation of U.S. application Ser. No.
17/201,892, filed Mar. 15, 2021, which is a continuation of U.S.
application Ser. No. 15/816,640, filed Nov. 17, 2017 (now U.S. Pat.
No. 10,967,560), which is a continuation of U.S. application Ser.
No. 14/950,567, filed Nov. 24, 2015 (now U.S. Pat. No. 9,855,369),
which is a continuation of U.S. application Ser. No. 14/530,499,
filed Oct. 31, 2014 (now U.S. Pat. No. 9,227,339), which is a
continuation of U.S. application Ser. No. 13/968,313, filed Aug.
15, 2013 (now U.S. Pat. No. 8,931,880), which is a continuation of
U.S. application Ser. No. 13/246,428, filed Sep. 27, 2011 (now U.S.
Pat. No. 9,149,952), which claims the benefit of U.S. provisional
App. Ser. No. 61/405,582, filed Oct. 21, 2010, each of which is
incorporated by reference in its entirety.
Claims
What is claimed is:
1. A bioprinter comprising: one or more printer heads, wherein each
printer head comprises a means for receiving and holding at least
one cartridge, and wherein each cartridge comprises a deposition
orifice and a bio-ink, the bio-ink comprising a solid or semi-solid
composition comprising living cells; a means for dispensing the
bio-ink of a selected cartridge by application of pressure to
extrude the bio-ink of the selected cartridge through the
deposition orifice; a means for determining a position of the
selected cartridge in three dimensions, comprising a sensor having
a sensor range threshold, such that a position of the cartridge is
determined when the deposition orifice reaches the sensor range
threshold; and a programmable computer processor for regulating the
pressure and the speed of the dispensing of the bio-ink
communicatively coupled to a means for positioning the selected
cartridge in three dimensions and the means for dispensing the
bio-ink.
2. The bioprinter of claim 1, wherein the means for dispensing the
bio-ink of a selected cartridge applies pressure via a piston,
compressed gas, hydraulics, or a combination thereof.
3. The bioprinter of claim 1, further comprising a means for
adjusting temperature.
4. The bioprinter of claim 3, further comprising a means for
adjusting the ambient temperature, the temperature of a cartridge,
the temperature of the bio-ink of the cartridge, the temperature of
the receiving surface, or a combination thereof.
5. The bioprinter of claim 4, wherein the means for adjusting
temperature is a heating element.
6. The bioprinter of claim 5, wherein the means for adjusting
temperature is a radiant heater, a convection heater, a conductive
heater, a fan heater, a heat exchanger, or a combination
thereof.
7. The bioprinter of claim 4, wherein the means for adjusting
temperature is a cooling element.
8. The bioprinter of claim 7, wherein the means for adjusting
temperature is a container of coolant, a chilled liquid, ice, a
radiant cooler, a convection cooler, a conductive cooler, a fan
cooler, or a combination thereof.
9. The bioprinter of claim 1, further comprising a means for
applying a wetting agent to one or more of: the printer stage; the
receiving surface; the deposition orifice; bio-ink; support
material; and the printed construct, wherein the wetting agent is
applied at one or more time points selected from: before the
bio-ink or support material is dispensed by the bioprinter,
substantially concurrently with dispensing, and after the bio-ink
or support material is dispensed by the bioprinter.
10. The bioprinter of claim 1, further comprising a receiving
surface for receiving one or more structures deposited from the
selected cartridge, wherein the receiving surface is substantially
flat.
11. The bioprinter of claim 1, further comprising a receiving
surface for receiving one or more structures deposited from the
selected cartridge, wherein the topography of the receiving surface
is designed to accommodate or influence one or more of the size,
shape, texture, or geometry of one or more deposited
structures.
12. The bioprinter of claim 1, wherein the computer processor is
programmable by a graphical user interface that is capable of
receiving input of a visual representation of a desired tissue
construct; and generating a series of commands, wherein the
commands are based on the visual representation inputted via the
graphical user interface.
13. The bioprinter of claim 12, wherein the visual representation
of a desired tissue construct is displayed on a display screen as a
three-dimensional rendering prior to executing a bioprinting
protocol on the bioprinter.
14. The bioprinter of claim 13, wherein the three-dimensional
rendering is adjustable in a plane or along a vector on the display
screen.
Description
BACKGROUND OF INVENTION
A number of pressing problems confront the healthcare industry. As
of December 2009 there were 105,305 patients registered by United
Network for Organ Sharing (UNOS) as needing an organ transplant.
Between January and September 2009, only 21,423 transplants were
performed. Each year more patients are added to the UNOS list than
transplants are performed, resulting in a net increase in the
number of patients waiting for a transplant. For example, at the
beginning of 2008, 75,834 people were registered as needing a
kidney; at the end of that year, the number had grown to 80,972.
16,546 kidney transplants were performed that year, but 33,005 new
patients were added to the list. The 2008 transplant rate for a
patient registered by UNOS as needing a kidney was 20%. The
mortality rate of waitlist patients was 7%.
Additionally, the research and development cost of a new
pharmaceutical compound is approximately $1.8 billion. See Paul, et
al. (2010). How to improve R&D productivity: the pharmaceutical
industry's grand challenge. Nature Reviews Drug Discovery
9(3):203-214. Drug discovery is the process by which drugs are
discovered and/or designed. The process of drug discovery generally
involves at least the steps of: identification of candidates,
synthesis, characterization, screening, and assays for therapeutic
efficacy. Despite advances in technology and understanding of
biological systems, drug discovery is still a lengthy, expensive,
and inefficient process with low rate of new therapeutic
discovery.
SUMMARY OF THE INVENTION
There is a need for tools and techniques that facilitate
application of regenerative medicine and tissue engineering
technologies to relieving the urgent need for tissues and organs.
There is also a need for tools and techniques that substantially
increase the number and quality of innovative, cost-effective new
medicines, without incurring unsustainable R&D costs.
Accordingly, the inventors describe herein devices, systems, and
methods for fabricating tissues and organs.
Described herein are bioprinters comprising: one or more printer
heads, wherein a printer head comprises a means for receiving and
holding at least one cartridge, and wherein said cartridge
comprises contents selected from one or more of: bio-ink and
support material; a means for calibrating the position of at least
one cartridge; and a means for dispensing the contents of at least
one cartridge. In one embodiment, a printer head described herein
comprises a means for receiving and holding one cartridge. In
another embodiment, a printer head described herein comprises a
means for receiving and holding more than one cartridge. In another
embodiment, the bioprinter further comprises a printer stage. In
another embodiment, the means for receiving and holding at least
one cartridge is selected from: magnetic attraction, a collet chuck
grip, a ferrule, a nut, a barrel adaptor, or a combination thereof.
In yet another embodiment, the means for receiving and holding at
least one cartridge is a collet chuck grip. In yet another
embodiment, the means for calibrating the position of at least one
cartridge of is selected from: laser alignment, optical alignment,
mechanical alignment, piezoelectric alignment, magnetic alignment,
electrical field or capacitance alignment, ultrasound alignment, or
a combination thereof. In yet another embodiment, the means for
calibrating the position of at least one cartridge is laser
alignment. In another embodiment, the means for dispensing the
contents of at least one cartridge is application of a piston,
application of pressure, application of compressed gas, hydraulics,
or a combination thereof. In yet another embodiment, the means for
dispensing the contents of at least one cartridge is application of
a piston. In yet another embodiment, the diameter of the piston is
less than the diameter of a cartridge. In another embodiment, the
bioprinter further comprises a means for adjusting temperature. In
yet another embodiment, the bioprinter further comprises a means
for adjusting the ambient temperature, the temperature of a
cartridge, the temperature of the contents of the cartridge, the
temperature of the receiving surface, or a combination thereof. In
yet another embodiment, the means for adjusting temperature is a
heating element. In yet another embodiment, the means for adjusting
temperature is a heater. In yet another embodiment, the means for
adjusting temperature is a radiant heater, a convection heater, a
conductive heater, a fan heater, a heat exchanger, or a combination
thereof. In yet another embodiment, the means for adjusting
temperature is a cooling element. In yet another embodiment, the
means for adjusting temperature is a container of coolant, a
chilled liquid, ice, a radiant cooler, a convection cooler, a
conductive cooler, a fan cooler, or a combination thereof. In yet
another embodiment, the temperature is adjusted to between about 40
and about 90.degree. C. In yet another embodiment, the temperature
is adjusted to between about 0 and about 10.degree. C. In another
embodiment, a bioprinter disclosed herein, further comprises a
means for applying a wetting agent to one or more of: the printer
stage; the receiving surface, the deposition orifice, bio-ink,
support material, or the printed construct.
Also disclosed herein are methods of calibrating the position of a
cartridge comprising a deposition orifice, wherein the cartridge is
attached to a bioprinter, comprising: calibrating the position of
the cartridge along at least one axis; wherein the axis is selected
from the x-axis, y-axis, and z-axis; and wherein each calibration
is made by use of a laser. In one embodiment, the methods comprise
activating the laser and generating at least one substantially
stable and/or substantially stationary laser beam, and where said
laser beam is horizontal to the ground. In another embodiment, the
methods comprise activating the laser and generating at least one
substantially stable and/or substantially stationary laser beam,
and where said laser beam is vertical to the ground. In yet another
embodiment, each calibration is made by use of first and a second
laser. In yet another embodiment, the first laser is vertical to
the ground and the second laser is horizontal to the ground. In
another embodiment, calibrating the position of the cartridge along
the y-axis by use of a horizontal laser comprises: positioning the
cartridge so that the cartridge is (i) located in a first y octant
and (ii) the dispensing orifice is below the upper threshold of the
laser beam; (a) moving the cartridge towards the laser beam and
stopping said movement as soon as the laser beam is interrupted by
the cartridge, wherein the position at which the laser beam is
interrupted by the cartridge is the first y position; (b)
re-positioning the cartridge so that the cartridge is located in
the second y octant and the dispensing orifice is below the upper
threshold of the laser beam; (c) moving the cartridge towards the
laser beam and stopping said movement as soon as the laser beam is
interrupted by the cartridge, wherein the position at which the
laser beam is interrupted is the second y position; (d) and
calculating the mid-point between the first y position and the
second y position. In another embodiment, calibrating the position
of the cartridge along the x-axis by use of a horizontal laser
comprises: (a) positioning the cartridge (i) at the mid-point
between the first y position and the second y position, and (ii)
outside the sensor threshold of the laser; (b) moving the cartridge
towards the sensor threshold and stopping said movement as soon as
the cartridge contacts the sensor threshold; (c) wherein the
position at which the cartridge contacts the sensor increased by
half the cartridge width is the x position. In another embodiment,
calibrating the position of the cartridge along the z-axis by use
of a horizontal laser comprises: (a) positioning the cartridge so
that the dispensing orifice is located above the laser beam; (b)
moving the cartridge towards the laser beam and stopping said
movement as soon as the laser beam is interrupted by the cartridge,
wherein the position at which the laser beam is interrupted is the
z position. In another embodiment, calibrating the position of the
cartridge along the y-axis by use of a vertical laser comprises:
(a) positioning the cartridge so that the cartridge is (i) located
in a first y octant and (ii) the dispensing orifice is outside the
sensor threshold of the laser beam; (b) moving the cartridge
towards the laser beam and stopping said movement as soon as the
laser beam is interrupted by the cartridge, wherein the position at
which the laser beam is interrupted by the cartridge is the first y
position; (c) re-positioning the cartridge so that the cartridge is
located in the second y octant and the dispensing orifice is
outside of the sensor threshold of the laser beam; (d) moving the
cartridge towards the laser beam and stopping said movement as soon
as the laser beam is interrupted by the cartridge, wherein the
position at which the laser beam is interrupted is the second y
position; (e) calculating the mid-point between the first y
position and the second y position; and (f) optionally, repeating
(a)-(e) and averaging calculated mid-points. In another embodiment,
calibrating the position of the cartridge along the x-axis by use
of a vertical laser comprises: (a) positioning the cartridge so
that the cartridge is (i) located in a first x octant and (ii) the
dispensing orifice is outside the sensor threshold of the laser
beam; (b) moving the cartridge towards the laser beam and stopping
said movement as soon as the laser beam is interrupted by the
cartridge, wherein the position at which the laser beam is
interrupted by the cartridge is the first x position; (c)
re-positioning the cartridge so that the cartridge is located in
the second x octant and the dispensing orifice is outside of the
sensor threshold of the laser beam; (d) moving the cartridge
towards the laser beam and stopping said movement as soon as the
laser beam is interrupted by the cartridge, wherein the position at
which the laser beam is interrupted is the second x position; (e)
calculating the mid-point between the first x position and the
second x position; and (f) optionally, repeating (a)-(e) and
averaging calculated mid-points. In another embodiment, calibrating
the position of the cartridge along the z-axis by use of a vertical
laser comprises: (a) positioning the printer head so that the
dispensing orifice is located above the laser beam and outside of
the laser sensor range threshold; (b) moving the printer head along
the z-axis the sensor threshold is reached; wherein, the z-position
is the position at which the laser sensor threshold is reached; and
optionally, repeating steps (a) and (b) and calculating average
z-positions. In another embodiment, calibrating the position of the
cartridge along the z-axis comprises: visually determining the
position of the dispensing orifice.
Further described herein are systems for calibrating the position
of a cartridge comprising a dispensing orifice, wherein the
cartridge is attached to a bioprinter, said system comprising: a
means for calibrating the position of the cartridge along at least
one axis, and wherein the axis is selected from the y-axis, x-axis,
and z-axis. In one embodiment, the means for calibrating the
cartridge is laser alignment, optical alignment, mechanical
alignment, piezoelectric alignment, magnetic alignment, electrical
field or capacitance alignment, ultrasound alignment, or a
combination thereof. In another embodiment, the means for
calibrating the cartridge is laser alignment. In yet another
embodiment, the laser alignment means comprises at least one laser,
selected from a horizontal laser and a vertical laser. In yet
another embodiment, the laser alignment means comprises a
horizontal laser and a vertical laser. In yet another embodiment,
the laser alignment means is accurate to .+-.40 .mu.m on the
vertical axis and .+-.20 on the horizontal axis.
Further described herein are methods for fabricating tissue
constructs, comprising: a computer module receiving input of a
visual representation of a desired tissue construct; a computer
module generating a series of commands, wherein the commands are
based on the visual representation and are readable by a
bioprinter; a computer module providing the series of commands to a
bioprinter; and the bioprinter depositing bio-ink and support
material according to the commands to form a construct with a
defined geometry. In some embodiments, a computer module comprises
a display screen. In further embodiments, a computer module
comprises a graphical user interface (GUI). In still further
embodiments, a user defines the content of one or more objects to
form a visual representation of a desired tissue construct using a
GUI provided by the computer module. In one embodiment, the display
screen consists essentially of a grid comprising a plurality of
objects of substantially the same shape and substantially equal
size. In yet another embodiment, each object is in the shape of a
circle. In yet another embodiment, the user defines the content of
one or more objects to form a visual representation of a desired
tissue construct. In yet another embodiment, the user defined
content of an object is selected from bio-ink or support material.
In further embodiments, the display screen consists of
three-dimensional rendering(s) that are input by the user
electronically or manually, whereby the various components of the
three-dimensional rendering can be adjusted in any suitable plane
or vector prior to executing a bioprinting protocol on the
bioprinter.
Further described herein are methods of attaching a cartridge to a
bioprinter, comprising: (a) inserting the cartridge into a collet
chuck, wherein the collet chuck is attached to a printer head of
the bioprinter; and (b) adjusting the outer collar of the collet
chuck; wherein the inserting and adjusting do not substantially
alter the position of the printer head.
Further described herein are cartridges for use with the
bioprinters described herein, comprising at least one orifice,
wherein the edges of the orifice are smooth or substantially
smooth. In one embodiment, the cartridge is a capillary tube or a
micropipette. In another embodiment, the cartridge comprises a
bio-ink. In yet another embodiment, the cartridge comprises a
support material. In yet another embodiment, the orifice is
circular or square. In yet another embodiment, the cartridge has an
internal diameter of about 1 .mu.m to about 1000 .mu.m. In yet
another embodiment, the cartridge has an internal diameter of about
500 .mu.m. In yet another embodiment, the cartridge has a volume of
about 1 .mu.l to about 50 .mu.l. In yet another embodiment, the
cartridge has a volume of about 5 .mu.l. In yet another embodiment,
the cartridge is marked to indicate the composition of the bio-ink.
In yet another embodiment, the cartridge is marked to indicate the
composition of the support material. In some embodiments, the
bio-ink and/or support material is primed. In further embodiments,
the bio-ink is primed by extruding the bio-ink to the level of the
dispensing orifice prior to initiating the bioprinter protocol. In
further embodiments, the support material is primed by extruding
the support material to the level of the dispensing orifice prior
to initiating the bioprinter protocol.
Further described herein are systems for attaching a cartridge to a
bioprinter, comprising: a means for receiving and securing a
cartridge to a printer head of a bioprinter; wherein use of the
means for receiving and securing the cartridge do not substantially
alter the position of the printer head. In some embodiments, the
means for receiving and securing the cartridge to a printer head is
selected from: magnetic attraction, a collet chuck grip, a ferrule,
a nut, a barrel adaptor, or a combination thereof. In one
embodiment, in the means for receiving and securing the cartridge
to a printer head is a collet.
Further described herein are receiving surfaces for receiving one
or more structures dispensed from bioprinters. In one embodiment,
the receiving surface is flat or substantially flat. In another
embodiment, the receiving surface is smooth or substantially
smooth. In yet another embodiment, the receiving surface is (a)
flat or substantially flat and (b) smooth or substantially smooth
or (c) defined or substantially defined. In another embodiment, the
topography of the receiving surface is designed to accommodate or
influence the size, shape, or texture, or geometry one or more
dispensed structures. In yet another embodiment, the receiving
surface comprises a solid material, a semi-solid material, or a
combination thereof. In yet another embodiment, the receiving
surface comprises glass, plastic, metal, a metal alloy, or a
combination thereof. In yet another embodiment, the receiving
surface comprises a gel. In yet another embodiment, the receiving
surface resists adhesion of the one or more structures. In yet
another embodiment, the receiving surface comprises polymerized
NovoGel.TM..
BRIEF DESCRIPTION OF FIGURES
FIG. 1 illustrates a non-limiting example of calibration of a
cartridge using a horizontal laser.
FIG. 2 illustrates a non-limiting example of calibration of a
cartridge using a vertical laser.
FIG. 3 illustrates a non-limiting example of a capillary priming
process.
FIG. 4 illustrates a non-limiting example of a two-dimensional
representation of a bio-printed tissue construct.
FIG. 5 illustrates a non-limiting example of a three-dimensional
construct generated by continuous deposition of PF-127 using a
NovoGen MMX.TM. bioprinter connected to a syringe with a 510 .mu.m
needle; in this case, a pyramid-shaped construct.
FIG. 6 illustrates a non-limiting example of a three-dimensional
construct generated by continuous deposition of PF-127 using a
NovoGen MMX.TM. bioprinter connected to a syringe with a 510 .mu.m
needle; in this case, cube-shaped (left) and hollow cube-shaped
(right) constructs.
DETAILED DESCRIPTION OF INVENTION
The invention relates to the fields of regenerative medicine,
tissue/organ engineering, biologic and medical research, and drug
discovery. More particularly, the invention relates to devices for
fabricating tissues and organs, systems and methods for calibrating
and using such devices, and tissues and organs fabricated by the
devices, systems, and methods disclosed herein.
Disclosed herein, in certain embodiments, are bioprinters
comprising: one or more printer heads, wherein a printer head
comprises a means for receiving and holding at least one cartridge,
and wherein said cartridge comprises contents selected from one or
more of: bio-ink and support material; a means for calibrating the
position of at least one cartridge; and a means for dispensing the
contents of at least one cartridge.
Also disclosed herein, in certain embodiments, are methods of
calibrating the position of a cartridge comprising a deposition
orifice, wherein the cartridge is attached to a bioprinter,
comprising: calibrating the position of the cartridge along at
least one axis; wherein the axis is selected from the x-axis,
y-axis, and z-axis; and wherein each calibration is made by use of
a laser.
Also disclosed herein, in certain embodiments, are systems for
calibrating the position of a cartridge comprising a deposition
orifice, wherein the cartridge is attached to a bioprinter, said
system comprising: a means for calibrating the position of the
cartridge along at least one axis, wherein the axis is selected
from the y-axis, x-axis, and z-axis.
Also disclosed herein, in certain embodiments, are methods for
fabricating tissue constructs, comprising: a computer module
receiving input of a visual representation of a desired tissue
construct; a computer module generating a series of commands,
wherein the commands are based on the visual representation and are
readable by a bioprinter; a computer module providing the series of
commands to a bioprinter; and the bioprinter depositing bio-ink and
support material according to the commands to form a construct with
a defined geometry.
Also disclosed herein, in certain embodiments, are methods of
attaching a cartridge to a bioprinter, comprising: (a) inserting
the cartridge into a collet chuck, wherein the collet chuck is
attached to a printer head of the bioprinter; and (b) adjusting the
outer collar of the collet chuck; wherein the inserting and
adjusting do not substantially alter the position of the printer
head.
Also disclosed herein, in certain embodiments, are systems for
attaching a cartridge to a bioprinter, comprising: a means for
receiving and securing a cartridge to a printer head of a
bioprinter; wherein use of the means for receiving and securing the
cartridge do not substantially alter the position of the printer
head.
Certain Definitions
Unless otherwise defined, all technical and scientific terms used
herein have the same meaning as commonly understood by one of
ordinary skill in the art to which this invention belongs. All
publications, patent applications, patents, and other references
mentioned herein are incorporated by reference in their
entirety.
As used in this specification and the appended claims, the singular
forms "a," "an," and "the" include plural references unless the
context clearly dictates otherwise. Thus, for example, references
to "a nucleic acid" includes one or more nucleic acids, and/or
compositions of the type described herein which will become
apparent to those persons skilled in the art upon reading this
disclosure and so forth. Any reference to "or" herein is intended
to encompass "and/or" unless otherwise stated.
As used herein, "allograft" means an organ or tissue derived from a
genetically non-identical member of the same species as the
recipient.
As used herein, "bio-ink" means a liquid, semi-solid, or solid
composition comprising a plurality of cells. In some embodiments,
bio-ink comprises cell solutions, cell aggregates, cell-comprising
gels, multicellular bodies, or tissues. In some embodiments, the
bio-ink additionally comprises support material. In some
embodiments, the bio-ink additionally comprises non-cellular
materials that provide specific biomechanical properties that
enable bioprinting.
As used herein, "bioprinting" means utilizing three-dimensional,
precise deposition of cells (e.g., cell solutions, cell-containing
gels, cell suspensions, cell concentrations, multicellular
aggregates, multicellular bodies, etc.) via methodology that is
compatible with an automated, computer-aided, three-dimensional
prototyping device (e.g., a bioprinter).
As used herein, "cartridge" means any object that is capable of
receiving (and holding) a bio-ink or a support material.
As used herein, a "computer module" means a software component
(including a section of code) that interacts with a larger computer
system. In some embodiments, a software module (or program module)
comes in the form of a file and typically handles a specific task
within a larger software system. In some embodiments, a module may
be included in one or more software systems. In other embodiments,
a module may be seamlessly integrated with one or more other
modules into one or more software systems. A computer module is
optionally a stand-alone section of code or, optionally, code that
is not separately identifiable. A key feature of a computer module
is that it allows an end user to use a computer to perform the
identified functions.
As used herein, "implantable" means biocompatible and capable of
being inserted or grafted into or affixed onto a living organism
either temporarily or substantially permanently.
As used herein, "organ" means a collection of tissues joined into
structural unit to serve a common function. Examples of organs
include, but are not limited to, skin, sweat glands, sebaceous
glands, mammary glands, bone, brain, hypothalamus, pituitary gland,
pineal body, heart, blood vessels, larynx, trachea, bronchus, lung,
lymphatic vessel, salivary glands, mucous glands, esophagus,
stomach, gallbladder, liver, pancreas, small intestine, large
intestine, colon, urethra, kidney, adrenal gland, conduit, ureter,
bladder, fallopian tube, uterus, ovaries, testes, prostate,
thyroid, parathyroid, meibomian gland, parotid gland, tonsil,
adenoid, thymus, and spleen.
As used herein, "patient" means any individual. The term is
interchangeable with "subject," "recipient," and "donor." None of
the terms should be construed as requiring the supervision
(constant or otherwise) of a medical professional (e.g., physician,
nurse, nurse practitioner, physician's assistant, orderly, hospice
worker, social worker, clinical research associate, etc.) or a
scientific researcher.
As used herein, "stem cell" means a cell that exhibits potency and
self-renewal. Stem cells include, but are not limited to,
totipotent cells, pluripotent cells, multipotent cells, oligopotent
cells, unipotent cells, and progenitor cells. Stem cells may be
embryonic stem cells, peri-natal stem cells, adult stem cells,
amniotic stem cells, and induced pluripotent stem cells.
As used herein, "tissue" means an aggregate of cells. Examples of
tissues include, but are not limited to, connective tissue (e.g.,
areolar connective tissue, dense connective tissue, elastic tissue,
reticular connective tissue, and adipose tissue), muscle tissue
(e.g., skeletal muscle, smooth muscle and cardiac muscle),
genitourinary tissue, gastrointestinal tissue, pulmonary tissue,
bone tissue, nervous tissue, and epithelial tissue (e.g., simple
epithelium and stratified epithelium), endoderm-derived tissue,
mesoderm-derived tissue, and ectoderm-derived tissue.
As used herein, "xenograft" means an organ or tissue derived from a
different species as the recipient.
Current Methods of Organ Transplants
Currently, there is no reliable method for de novo organ synthesis.
Organs are only derived from living donors (e.g., for kidney and
liver donations), deceased donors (e.g., for lung and heart
donations) and, in a few cases, animals (e.g., porcine heart
valves). Thus, patients needing an organ transplant must wait for a
donor organ to become available. This results in a shortage of
available organs. Additionally, reliance on organs harvested from a
living organism increases the chance of transplant rejection.
Transplant Rejections
In certain instances, a patient receiving an organ transplant
experience hyperacute rejection. As used herein, "hyperacute
rejection" means a complement-mediated immune response resulting
from the recipient's having pre-existing antibodies to the donor
organ. Hyperacute rejection occurs within minutes and is
characterized by blood agglutination. If the transplanted organ is
not immediately removed, the patient may become septic. Xenografts
will produce hyperacute rejection unless the recipient is first
administered immunosuppressants. In some embodiments, a tissue or
organ fabricated de novo will not comprise any antigens and thus
cannot be recognized by any antibodies of the recipient.
In certain instances, a patient receiving an organ transplant
experiences acute rejection. As used herein, "acute rejection"
means an immune response that begins about one week after
transplantation to about one year after transplantation. Acute
rejection results from the presence of foreign HLA molecules on the
donor organ. In certain instances, APCs recognize the foreign HLAs
and activate helper T cells. In certain instances, helper T cells
activate cytotoxic T cells and macrophages. In certain instances,
the presence of cytotoxic T cells and macrophages results in the
death of cells with the foreign HLAs and thus damage (or death) of
the transplanted organ. Acute rejection occurs in about 60-75% of
kidney transplants, and 50-60% of liver transplants. In some
embodiments, a tissue or organ fabricated de novo will not comprise
any HLAs and thus will not result in the activation of helper T
cells.
In certain instances, a patient receiving an organ transplant
experiences chronic rejection. As used herein, "chronic rejection"
means transplant rejection resulting from chronic inflammatory and
immune responses against the transplanted tissue. In some
embodiments, a tissue or organ fabricated de novo will not comprise
any antigens or foreign HLAs and thus will not induce inflammatory
or immune responses.
In certain instances, a patient receiving an organ transplant
experiences chronic allograft vasculopathy (CAV). As used herein,
"chronic allograft vasculopathy" means loss of function in
transplanted organs resulting from fibrosis of the internal blood
vessels of the transplanted organ. In certain instances, CAV is the
result of long-term immune responses to a transplanted organ. In
some embodiments, a tissue or organ fabricated de novo will not
comprise any antigens or foreign HLAs and thus will not result in
an immune response.
In order to avoid transplant rejection, organ recipients are
administered immunosuppressant drugs. Immunosuppressants include,
but are not limited to, corticosteroids (e.g., prednisone and
hydrocortisone), calcineurin inhibitors (e.g., cyclosporine and
tacrolimus), anti-proliferative agents (e.g., azathioprine and
mycophenolic acid), antibodies against specific components of the
immune system (e.g., basiliximab, dacluzimab, anti-thymocyte
globulin (ATG) and anti-lymphocyte globulin (ALG) and mTOR
inhibitors (e.g., sirolimus and everolimus)). However,
immunosuppressants have several negative side-effects including,
but not limited to, susceptibility to infection (e.g., infection by
Pneumocystis carinii pneumonia (PCP), cytomegalovirus pneumonia
(CMV), herpes simplex virus, and herpes zoster virus) and the
spread of malignant cells, hypertension, dyslipidaemia,
hyperglycemia, peptic ulcers, liver and kidney injury, and
interactions with other medicines. In some embodiments, a tissue or
organ fabricated de novo will not result in an immune response and
thus will not require the administration of an
immunosuppressant.
Infections
In certain instances, a donor organ may be infected with an
infectious agent. Following the transplant of the infected organ,
the infectious agent is able to spread throughout the donor (due in
part to the use of immunosuppressant drugs). By way of non-limiting
example, recipients have contracted HIV, West Nile Virus, rabies,
hepatitis C, lymphocytic choriomeningitis virus (LCMV),
tuberculosis, Chagas disease, and Creutzfeldt-Jakob disease from
transplanted organs. While such infections are rare, they can
nevertheless occur--social histories for deceased donors are often
inaccurate as they are necessarily derived from next-of-kin,
serological tests may produce false-negative results if
seroconversion has not occurred, or serological tests may also
produce false-negatives due to hemodilution following blood
transfusion. Further, many uncommon infectious agents are not
screened for due to the limited time a harvested organ is viable.
In some embodiments, a tissue or organ fabricated de novo will not
comprise any infectious agents.
Donor Complications
A living donor may also experience complications as a result of
donating an organ. These complications include nosocomial
infections, allergic reactions to the anesthesia, and surgical
errors. Further, an organ donor may one day find themselves in need
of the organ they donated. For example, the remaining kidney of a
kidney donor or the remaining lobe of a liver donor may become
damaged. In some embodiments, a tissue or organ fabricated de novo
obviates the need for donor organs and thus will avoid negative
side-effects to the donor.
In light of the shortage of available organs and all the
complications that can follow a donor organ transplant, there is a
need for a method of de novo fabrication of tissues and organs.
Tissue Engineering
Tissue engineering is an interdisciplinary field that applies and
combines the principles of engineering and life sciences toward the
development of biological substitutes that restore, maintain, or
improve tissue function through augmentation, repair, or
replacement of an organ or tissue. The basic approach to classical
tissue engineering is to seed living cells into a biocompatible and
eventually biodegradable environment (e.g., a scaffold), and then
culture this construct in a bioreactor so that the initial cell
population can expand further and mature to generate the target
tissue upon implantation. With an appropriate scaffold that mimics
the biological extracellular matrix (ECM), the developing tissue
may adopt both the form and function of the desired organ after in
vitro and in vivo maturation. However, achieving high enough cell
density with a native tissue-like architecture is challenging due
to the limited ability to control the distribution and spatial
arrangement of the cells throughout the scaffold. These limitations
may result in tissues or organs with poor mechanical properties
and/or insufficient function. Additional challenges exist with
regard to biodegradation of the scaffold, entrapment of residual
polymer, and industrial scale-up of manufacturing processes.
Scaffoldless approaches have been attempted. Current scaffoldless
approaches are subject to several limitations:
Complex geometries, such as multi-layered structures wherein each
layer comprises a different cell type, may require definitive,
high-resolution placement of cell types within a specific
architecture to reproducibly achieve a native tissue-like
outcome.
Scale and geometry are limited by diffusion and/or the requirement
for functional vascular networks for nutrient supply.
The viability of the tissues may be compromised by confinement
material that limits diffusion and restricts the cells' access to
nutrients.
Disclosed herein, in certain embodiments, are devices, systems, and
methods that generate a three-dimensional tissue construct. The
devices, systems, and methods disclosed herein utilize a
three-phase process: (i) pre-processing, or bio-ink preparation,
(ii) processing, i.e. the actual automated delivery/printing of the
bio-ink particles into the bio-paper by the bioprinter, and (iii)
post-processing, i.e., the maturation/incubation of the printed
construct in the bioreactor. Final structure formation takes place
during post-processing via the fusion of the bio-ink particles. The
devices, systems, and methods disclosed herein have the following
advantages:
They are capable of producing cell-comprising tissues and/or
organs.
They mimic the environmental conditions of the natural
tissue-forming processes by exploiting principles of developmental
biology.
They can achieve a broad array of complex topologies (e.g.,
multilayered structures, repeating geometrical patterns, segments,
sheets, tubes, sacs, etc.).
They are compatible with automated means of manufacturing and are
scalable.
Bioprinting enables improved methods of generating cell-comprising
implantable tissues that are useful in tissue repair, tissue
augmentation, tissue replacement, and organ replacement.
Additionally, bioprinting enables improved methods of generating
micro-scale tissue analogs including those useful for in vitro
assays.
Bioprinting
Disclosed herein, in certain embodiments, are devices, systems, and
methods for fabricating tissues and organs. In some embodiments,
the devices are bioprinters. In some embodiments, the methods
comprise the use bioprinting techniques. In further embodiments,
the tissues and organs fabricated by use of the devices, systems,
and methods described herein are bioprinted.
In some embodiments, bioprinted cellular constructs, tissues, and
organs are made with a method that utilizes a rapid prototyping
technology based on three-dimensional, automated, computer-aided
deposition of cells, including cell solutions, cell suspensions,
cell-comprising gels or pastes, cell concentrations, multicellular
bodies (e.g., cylinders, spheroids, ribbons, etc.), and support
material onto a biocompatible surface (e.g., composed of hydrogel
and/or a porous membrane) by a three-dimensional delivery device
(e.g., a bioprinter). As used herein, in some embodiments, the term
"engineered," when used to refer to tissues and/or organs means
that cells, cell solutions, cell suspensions, cell-comprising gels
or pastes, cell concentrates, multicellular aggregates, and layers
thereof are positioned to form three-dimensional structures by a
computer-aided device (e.g., a bioprinter) according to computer
code. In further embodiments, the computer script is, for example,
one or more computer programs, computer applications, or computer
modules. In still further embodiments, three-dimensional tissue
structures form through the post-printing fusion of cells or
multicellular bodies similar to self-assembly phenomena in early
morphogenesis.
While a number of methods are available to arrange cells,
multicellular aggregates, and/or layers thereof on a biocompatible
surface to produce a three-dimensional structure including manual
placement, positioning by an automated, computer-aided machine such
as a bioprinter is advantageous. Advantages of delivery of cells or
multicellular bodies with this technology include rapid, accurate,
and reproducible placement of cells or multicellular bodies to
produce constructs exhibiting planned or pre-determined
orientations or patterns of cells, multicellular aggregates and/or
layers thereof with various compositions. Advantages also include
assured high cell density, while minimizing cell damage.
In some embodiments, methods of bioprinting are continuous and/or
substantially continuous. A non-limiting example of a continuous
bioprinting method is to dispense bio-ink from a bioprinter via a
dispense tip (e.g., a syringe, capillary tube, etc.) connected to a
reservoir of bio-ink. In further non-limiting embodiments, a
continuous bioprinting method is to dispense bio-ink in a repeating
pattern of functional units. In various embodiments, a repeating
functional unit has any suitable geometry, including, for example,
circles, squares, rectangles, triangles, polygons, and irregular
geometries. In further embodiments, a repeating pattern of
bioprinted function units comprises a layer and a plurality of
layers are bioprinted adjacently (e.g., stacked) to form an
engineered tissue or organ. In various embodiments, 2, 3, 4, 5, 6,
7, 8, 9, 10, 11, 12, 13, 14, 15, or more layers are bioprinted
adjacently (e.g., stacked) to form an engineered tissue or
organ.
In some embodiments, a bioprinted functional unit repeats in a
tessellated pattern. A "tessellated pattern" is a plane of figures
that fills the plane with no overlaps and no gaps. An advantage of
continuous and/or tessellated bioprinting can include an increased
production of bioprinted tissue. Increased production can include
achieving increased scale, increased complexity, or reduced time or
cost of production. Another non-limiting potential advantage can be
reducing the number of calibration events that are required to
complete the bioprinting of a three-dimensional construct.
Continuous bioprinting may also facilitate printing larger tissues
from a large reservoir of bio-ink, optionally using a syringe
mechanism.
Methods in continuous bioprinting may involve optimizing and/or
balancing parameters such as print height, pump speed, robot speed,
or combinations thereof independently or relative to each other. In
one example, the bioprinter head speed for deposition was 3 mm/s,
with a dispense height of 0.5 mm for the first layer and dispense
height was increased 0.4 mm for each subsequent layer. In some
embodiments, the dispense height is approximately equal to the
diameter of the bioprinter dispense tip. Without limitation a
suitable and/or optimal dispense distance does not result in
material flattening or adhering to the dispensing needle. In
various embodiments, the bioprinter dispense tip has an inner
diameter of about, 20, 50, 100, 150, 200, 250, 300, 350, 400, 450,
500, 550, 600, 650, 700, 750, 800, 850, 900, 950, 1000 .mu.m, or
more, including increments therein. In various embodiments, the
bio-ink reservoir of the bioprinter has a volume of about 0.5, 1,
2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60,
65, 70, 75, 80, 85, 90, 95, 100 cubic centimeters, or more,
including increments therein. The pump speed may be suitable and/or
optimal when the residual pressure build-up in the system is low.
Favorable pump speeds may depend on the ratio between the
cross-sectional areas of the reservoir and dispense needle with
larger ratios requiring lower pump speeds. In some embodiments, a
suitable and/or optimal print speed enables the deposition of a
uniform line without affecting the mechanical integrity of the
material.
The inventions disclosed herein include business methods. In some
embodiments, the speed and scalability of the devices and methods
disclosed herein are utilized to design, build, and operate
industrial and/or commercial facilities for production of
engineered tissues and/or organs. In further embodiments, the
engineered tissues and/or organs are produced, stored, distributed,
marketed, advertised, and sold as, for example, materials, tools,
and kits for medical treatment of tissue damage, tissue disease,
and/or organ failure or materials, tools, and kits to conduct
biological assays and/or drug screening as a service.
Bioprinter
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, a bioprinter
is any instrument that automates a bioprinting process. In certain
embodiments, a bioprinter disclosed herein comprises: one or more
printer heads, wherein a printer head comprises a means for
receiving and holding at least one cartridge, and wherein said
cartridge comprises contents selected from one or more of: bio-ink
and support material; a means for calibrating the position of at
least one cartridge; and a means for dispensing the contents of at
least one cartridge.
In various embodiments, a bioprinter dispenses bio-ink and/or
support material in pre-determined geometries (e.g., positions,
patterns, etc.) in two or three dimensions. In some embodiments, a
bioprinter achieves a particular geometry by moving a printer head
relative to a printer stage or receiving surface adapted to receive
bioprinted materials. In other embodiments, a bioprinter achieves a
particular geometry by moving a printer stage or receiving surface
relative to a printer head. In certain embodiments, the bioprinter
is maintained in a sterile environment.
In some embodiments, a bioprinter disclosed herein comprises one or
more printer heads. In further embodiments, a printer head
comprises a means for receiving and holding at least one cartridge.
In some embodiments, a printer head comprises a means for receiving
and holding more than one cartridge. In some embodiments, the means
for receiving and holding at least one cartridge is selected from:
magnetic attraction, a collet chuck grip, a ferrule, a nut, a
barrel adapter, or a combination thereof. In some embodiments, the
means for receiving and holding at least one cartridge is a collet
chuck grip.
In some embodiments, a bioprinter disclosed herein comprises a
means for calibrating the position of at least one cartridge. In
some embodiments, the means for calibrating the position of at
least one cartridge of is selected from: laser alignment, optical
alignment, mechanical alignment, piezoelectric alignment, magnetic
alignment, electrical field or capacitance alignment, ultrasound
alignment, or a combination thereof. In some embodiments, the means
for calibrating the position of at least one cartridge is laser
alignment.
In some embodiments, a bioprinter disclosed herein comprises a
means for dispensing the contents of at least one cartridge. In
some embodiments, the means for dispensing the contents of at least
one cartridge is application of a piston, application of pressure,
application of compressed gas, application of hydraulics, or
application of a combination thereof. In some embodiments, the
means for dispensing the contents of at least one cartridge is
application of a piston. In some embodiments, the diameter of the
piston is less than the diameter of a cartridge.
In some embodiments, a bioprinter disclosed herein further
comprises a receiving surface. In further embodiments, a receiving
surface is a non-cytotoxic surface onto which a bioprinter
dispenses bio-ink and/or support material. In some embodiments, a
bioprinter disclosed herein further comprises a printer stage. In
further embodiments, a receiving surface is a surface of a printer
stage. In other embodiments, a receiving surface is component
separate from a printer stage, but is affixed to or supported by a
stage. In some embodiments the receiving surface is flat or
substantially flat. In some embodiments the surface is smooth or
substantially smooth. In other embodiments, the surface is both
substantially flat and substantially smooth. In still further
embodiments the receiving surface is designed specifically to
accommodate the shape, size, texture, or geometry of the bioprinted
structure. In still further embodiments, the receiving surface
controls or influences the size, shape, texture, or geometry of a
bioprinted construct.
In some embodiments, a bioprinter disclosed herein further
comprises a means for adjusting temperature. In some embodiments,
the means for adjusting temperature adjusts and/or maintains the
ambient temperature. In other various embodiments, the means for
adjusting temperature adjusts and/or maintains the temperature of,
by way of non-limiting example, the print head, cartridge, contents
of the cartridge (e.g., bio-ink, support material, etc.), the
printer stage, and the receiving surface.
In some embodiments, the means for adjusting temperature is a
heating element. In some embodiments, the means for adjusting
temperature is a heater. In some embodiments, the means for
adjusting temperature is a radiant heater, a convection heater, a
conductive heater, a fan heater, a heat exchanger, or a combination
thereof. In some embodiments, the means for adjusting temperature
is a cooling element. In some embodiments, the means for adjusting
temperature is a container of coolant, a chilled liquid, ice, or a
combination thereof. In some embodiments, the means for adjusting
temperature is a radiant cooler, convection cooler, a conductive
cooler, a fan cooler, or a combination thereof.
In various embodiments, the means for adjusting temperature adjusts
a temperature to about 0, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50,
55, 60, 65, 70, 75, 80, 85, or 90.degree. C. including increments
therein. In some embodiments, temperature is adjusted to between
about 40.degree. C. and about 90.degree. C. In other embodiments,
temperature is adjusted to between about 0.degree. C. and about
10.degree. C.
In some embodiments, a bioprinter disclosed herein, further
comprises a means for applying a wetting agent to one or more of:
the printer stage; the receiving surface, the deposition orifice,
bio-ink, support material, or the printed construct. In some
embodiments, the means for applying the wetting agent is any
suitable method of applying a fluid (e.g., a sprayer, a pipette, an
inkjet, etc.). In some embodiments, the wetting agent is water,
tissue culture media, buffered salt solutions, serum, or a
combination thereof. In further embodiments, a wetting agent is
applied after the bio-ink or supporting material is dispensed by
the bioprinter. In some embodiments, a wetting agent is applied
simultaneously or substantially simultaneously with the bio-ink or
supporting material being dispensed by the bioprinter. In some
embodiments, a wetting agent is applied prior to the bio-ink or
supporting material being dispensed by the bioprinter.
Printer Head
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, a bioprinter
disclosed herein comprises one or more printer heads. In further
embodiments, a printer head comprises a means for receiving and
holding at least one cartridge. In still further embodiments, a
printer head attaches at least one cartridge to a bioprinter.
Many means for receiving and holding at least one cartridge are
suitable. Suitable means for receiving and holding at least one
cartridge include those that reliably, precisely, and securely
attach at least one cartridge to a bioprinter. In various
embodiments, the means for receiving and holding at least one
cartridge is, by way of non-limiting example, magnetic attraction,
a collet chuck grip, a ferrule, a nut, a barrel adapter, or a
combination thereof.
In some embodiments, a printer head disclosed herein receives and
holds one cartridge. In various other embodiments, a printer head
disclosed herein receives and holds 2, 3, 4, 5, 6, 7, 8, 9, 10, or
more cartridges simultaneously. In further embodiments, a printer
head disclosed herein further comprises a means to select a
cartridge to be employed in bioprinting from among a plurality of
cartridges received and held.
In some embodiments, a printer head disclosed herein further
comprises (or is in fluid communication with) a reservoir to
contain bio-ink and/or support materials beyond the capacity of the
one or more cartridges. In further embodiments, a reservoir
supplies bio-ink and/or support materials to one or more cartridges
for dispensing via a dispensing orifice. Printer head
configurations including a reservoir are particularly useful in
continuous or substantially continuous bioprinting applications.
Many volumes are suitable for a reservoir disclosed herein. In
various embodiments, a reservoir has an internal volume of, for
example, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, 30, 35, 40, 45,
50, 55, 60, 65, 70, 75, 80, 85, 90, 95, 100, 150, 200, 250, 300,
350, 400, 450, 500 ml or more, including increments therein.
In some embodiments, bioprinting involves using a computer to
configure parameters such as print height, pump speed, robot speed,
or combinations thereof independently or relative to each other. In
further embodiments, computer code specifies the positioning of a
printer head to configure printer head height above a receiving
surface. In further embodiments, computer code specifies the
direction and speed of the motion of a printer head to configure
dispensing characteristics for bio-ink and/or support material.
Cartridges
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, a cartridge
attached to the bioprinter comprises bio-ink or support material.
In some embodiments, the bioprinter dispenses bio-ink or support
material in a specific pattern and at specific positions in order
to form a specific cellular construct, tissue, or organ. In order
to fabricate complex tissue constructs, the bioprinter deposits the
bio-ink or support material at precise speeds and in uniform
amounts. Thus, there is a need for a cartridge with (a) a
dispensing orifice that is smooth or substantially smooth, and (b)
an internal surface that is smooth or substantially smooth. As used
herein, "cartridge" means any object that is capable of receiving
(and holding) a bio-ink and/or support material.
In some embodiments, a cartridge disclosed herein comprises
bio-ink. In some embodiments, a cartridge disclosed herein
comprises support material. In some embodiments, a cartridge
disclosed herein comprises a combination of bio-ink and support
material.
Disclosed herein, in certain embodiments, are cartridges for use
with a bioprinter disclosed herein, comprising at least one
dispensing orifice. In some embodiments, a cartridge comprises one
dispensing orifice. In various other embodiments, a cartridge
comprises 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 20, 30,
40, 50, 60, 70, 80, 90, 100, or more dispensing orifices. In
further embodiment, the edges of a dispensing orifice are smooth or
substantially smooth.
Many shapes are suitable for the dispensing orifices disclosed
herein. In various embodiments, suitable shapes for dispensing
orifices include, by way of non-limiting examples, circular, ovoid,
triangular, square, rectangular, polygonal, and irregular. In some
embodiments, the orifice is circular. In other embodiments, the
orifice is square. In yet other embodiments, the orifice is oval,
oblong, or rectangular and dispenses solid or semi-solid bio-ink
and/or support materials in a ribbon-like form.
In some embodiments, the internal surface of the cartridge is
smooth or substantially smooth. In some embodiments, the cartridge
is comprised of a rigid structure to facilitate calibration. In
some embodiments, the walls of the cartridge are comprised of a
material that resists attachment of cells. In some embodiments, the
cartridges are comprised of a material that is biocompatible.
Many types of cartridges are suitable for use with bioprinters
disclosed herein and the methods of using the same. In some
embodiments, a cartridge is compatible with bioprinting that
involves extruding a semi-solid or solid bio-ink or a support
material through one or more dispensing orifices. In some
embodiments, a cartridge is compatible with bioprinting that
involves dispensing a liquid or semi-solid cell solution, cell
suspension, or cell concentration through one or more dispensing
orifices. In some embodiments, a cartridge is compatible with
non-continuous bioprinting. In some embodiments, a cartridge is
compatible with continuous and/or substantially continuous
bioprinting.
In some embodiments, a cartridge is a capillary tube or a
micropipette. In some embodiments, a cartridge is a syringe or a
needle. Many internal diameters are suitable for substantially
round or cylindrical cartridges. In various embodiments, suitable
internal diameters include, by way of non-limiting examples, 1, 10,
50, 100, 200, 300, 400, 500, 600, 700, 800, 900, 1000 or more
.mu.m, including increments therein. In other various embodiments,
suitable internal diameters include, by way of non-limiting
examples, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 20, 30, 40, 50, 60, 70,
80, 90, 100 or more mm, including increments therein. In some
embodiments, a cartridge has an internal diameter of about 1 .mu.m
to about 1000 .mu.m. In a particular embodiment, a cartridge has an
internal diameter of about 500 .mu.m. In another particular
embodiment, a cartridge has an internal diameter of about 250
.mu.m. Many internal volumes are suitable for the cartridges
disclosed herein. In various embodiments, suitable internal volumes
include, by way of non-limiting examples, 1, 10, 20, 30, 40, 50,
100, 200, 300, 400, 500, 600, 700, 800, 900, 1000 or more .mu.l,
including increments therein. In other various embodiments,
suitable internal volumes include, by way of non-limiting examples,
1, 2, 3, 4, 5, 10, 20, 30, 40, 50, 60, 70, 80, 90, 100, 200, 300,
400, 500 or more ml, including increments therein. In some
embodiments, a cartridge has a volume of about 1 .mu.l to about 50
.mu.l. In a particular embodiment, a cartridge has a volume of
about 5 .mu.l.
In some embodiments, a cartridge is compatible with ink-jet
printing of bio-ink and/or support material onto a receiving
surface such as that described in U.S. Pat. No. 7,051,654. In
further embodiments, a cartridge includes dispensing orifices in
the form of voltage-gated nozzles or needles under the control of
the computer code described herein.
In some embodiments, the cartridge is primed. In some embodiments,
priming the cartridge increases the accuracy of the dispensing,
deposition, or extrusion process. As used herein, "primed" means
the contents of the cartridge are made ready for dispensing,
deposition, or extrusion by compacting and advancing the contents
of the cartridge until the material to be dispensed (bio-ink or
supporting material) is located in a position in contact with the
dispensing orifice. In some embodiments, the cartridge is primed
when the contents are compact or substantially compact, and the
contents are in physical contact with the orifice of the
cartridge.
In some embodiments, a cartridge is marked to indicate the
composition of its contents. In further embodiments, a cartridge is
marked to indicate the composition of a bio-ink and/or support
material contained therein. In some embodiments, the surface of the
cartridge is colored. In some embodiments, the outer surface of the
cartridge is dyed, painted, marked with a pen, marked by a sticker,
or a combination thereof.
In some embodiments, the outer surface of a cartridge is marked to
increase the opacity of the surface of the cartridge (e.g., to
increase the amount of a laser beam that is reflected off the
surface of the cartridge). In some embodiments, the surface of a
cartridge is colored. In some embodiments, the outer surface of a
cartridge is scored. As used herein, "scored" means marking the
surface of a cartridge to reduce the smoothness of the surface. Any
suitable method is used to score the surface of a cartridge (e.g.,
application of an acidic substance, application of a caustic
substance, application of an abrasive substance, etc.). In some
embodiments, the outer surface of a cartridge is painted, polished
(e.g., fire polished), etched (e.g., laser etched), marked with a
pen, marked by a sticker, or a combination thereof.
Grip
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, a cartridge
attached to a bioprinter comprises bio-ink and/or support material.
In some embodiments, the bioprinter dispenses the bio-ink and/or
support material in a specific pattern and at specific positions in
order to form a specific cellular construct, tissue, or organ. In
some embodiments, a cartridge comprising bio-ink is disposable. In
some embodiments, the cartridge is ejected from the bioprinter
following extrusion of the contents. In some embodiments, a new
cartridge is subsequently attached to the bioprinter.
In order to fabricate complex structures, the bioprinters disclosed
herein dispense bio-ink and/or support material from a cartridge
with a suitable repeatable accuracy. In various embodiments,
suitable repeatable accuracies include those of about .+-.5, 10,
20, 30, 40, or 50 .mu.m on any axis. In some embodiments, the
bioprinters disclosed herein dispense bio-ink and/or support
material from a cartridge with a repeatable accuracy of about
.+-.20 .mu.m. However, uncontrolled removal and insertion of
cartridges can result in alterations of the position of the printer
head (and thus the cartridges) with respect to the tissue
construct, such that precision of the placement of the first
bio-ink particle deposited from a new cartridge may vary relative
to the last bio-ink particle deposited from the previous cartridge.
Thus, there is a need for a method of attaching and securing a
cartridge to a printer head, wherein said attaching and securing
produce minimal alterations in the position of the printer
head.
Disclosed herein, in certain embodiments, are methods of attaching
a cartridge to a bioprinter, comprising: (a) inserting the
cartridge into a collet chuck, wherein the collet chuck is attached
to a printer head of the bioprinter; and (b) adjusting the outer
collar of the collet chuck; wherein the inserting and adjusting do
not substantially alter the position of the printer head.
Disclosed herein, in certain embodiments, are systems for attaching
a cartridge to a bioprinter, comprising: a means for receiving and
securing a cartridge to a printer head of a bioprinter; wherein use
of the means for receiving and securing the cartridge do not
substantially alter the position of the printer head. In some
embodiments, the means for receiving and securing the cartridge to
a printer head is a chuck or ferrule. As used herein, "chuck" means
a holding device consisting of adjustable jaws. In some
embodiments, the means for receiving and securing the cartridge to
a printer head is a collet. As used herein, "collet" means a
subtype of chuck--that forms a collar around the object to be held
and exerts a strong clamping. As used herein, "ferrule" means a
band (e.g., a metal band) used to secure one object to another. In
some embodiments, the means for receiving and securing the
cartridge to a printer head is a barrel adaptor. As used herein,
"barrel adaptor" means a threaded tube used to secure one object to
another.
Receiving Surface
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, the bioprinter
dispenses a plurality of elements, sections, and/or areas of
bio-ink and/or support material onto a receiving surface. In
further embodiments, dispensing occurs in a specific pattern and at
specific positions. In still further embodiments, the locations at
which the bioprinter deposits bio-ink and/or support material onto
a receiving surface are defined by user input and translated into
computer code.
In some embodiments, each of the elements, sections, and/or areas
of bio-ink and/or support material has dimensions of less than 300
mm.times.300 mm.times.160 mm. By way of example only, the
dimensions of a section of bio-ink or support material may be 75
mm.times.5.0 mm.times.5.0 mm; 0.3 mm.times.2.5 mm.times.2.5 mm; 1
mm.times.1 mm.times.50 mm; or 150 mm.times.150 mm.times.80 mm. Due
to the generally small size of each section, and in some cases, the
high degree of precision required, minute imperfections in the
receiving surface may result in imperfections (and possibly,
failure) of a cellular construct, tissue, or organ. Thus, there is
a need for a substantially smooth and substantially flat receiving
surface, or a defined or substantially defined receiving surface,
that is able to receive sections of bio-ink and/or support
material.
Disclosed herein, in certain embodiments, are receiving surfaces
for receiving one or more structures generated by the bioprinter
disclosed herein. In some embodiments, the receiving surface is
flat or substantially flat. In some embodiments, the receiving
surface is smooth or substantially smooth. In some embodiments, the
receiving surface is flat or substantially flat. In some
embodiments, the receiving surface is defined or substantially
defined. In other embodiments the receiving surface is designed
specifically to accommodate the shape, size, texture, or geometry
of a specific bioprinted structure. In further embodiments, the
receiving surface controls or influences the size, shape, texture,
or geometry of a bioprinted construct.
In some embodiments, the receiving surface comprises a solid
material, a semi-solid material, or a combination thereof. In some
embodiments, the receiving surface comprises glass, coated glass,
plastic, coated plastic, metal, a metal alloy, or a combination
thereof. In some embodiments, the receiving surface comprises a
gel. In some embodiments, the receiving surface and any coatings
thereon are biocompatible. In various embodiments, the receiving
surface comprises any of the support materials and/or confinement
materials disclosed herein. In specific embodiments, the receiving
surface comprises polymerized NovoGel.TM. or polymerized agarose,
polymerized gelatin, extracellular matrix (or components thereof),
collagen, or a combination thereof.
Software
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, one or more
cartridges attached to the bioprinter comprises bio-ink and/or
support material. In some embodiments, the bioprinter dispenses
bio-ink or support material in a specific pattern and at specific
positions in order to form a specific cellular construct, tissue,
or organ.
In order to fabricate complex tissue constructs, the bioprinter
deposits the bio-ink or support material at precise locations (in
two or three dimensions) on a receiving surface. In some
embodiments, the locations at which the bioprinter deposits bio-ink
and/or support material are defined by user input and translated
into computer code. In further embodiments, the computer code
includes a sequence of instructions, executable in the central
processing unit (CPU) of a digital processing device, written to
perform a specified task. In some embodiments, additional
bioprinting parameters including, by way of non-limiting examples,
print height, pump speed, robot speed, and/or control of variable
dispensing orifices are defined by user input and translated into
computer code. In other embodiments, such bioprinting parameters
are not directly defined by user input, but are derived from other
parameters and conditions by the computer code described
herein.
Disclosed herein, in certain embodiments, are methods for
fabricating tissue constructs, tissues, and organs, comprising: a
computer module receiving input of a visual representation of a
desired tissue construct; a computer module generating a series of
commands, wherein the commands are based on the visual
representation and are readable by a bioprinter; a computer module
providing the series of commands to a bioprinter; and the
bioprinter depositing bio-ink and/or support material according to
the commands to form a construct with a defined geometry.
Computer Readable Medium
In some embodiments, the locations at which the bioprinter deposits
the bio-ink and/or support material are defined by user input and
translated into computer code. In some embodiments, the devices,
systems, and methods disclosed herein further comprise computer
readable media or media encoded with computer readable program
code. In further embodiments, a computer readable medium is a
tangible component of a digital processing device such as a
bioprinter (or a component thereof) or a computer connected to a
bioprinter (or a component thereof). In still further embodiments,
a computer readable medium is optionally removable from a digital
processing device. In some embodiments, a computer readable medium
includes, by way of non-limiting examples, CD-ROMs, DVDs, flash
memory devices, solid state memory, magnetic disk drives, magnetic
tape drives, optical disk drives, cloud computing systems and
services, and the like.
Computer Modules
In some embodiments, the devices, systems, and methods described
herein comprise software, server, and database modules. In some
embodiments, a "computer module" is a software component (including
a section of code) that interacts with a larger computer system. In
further embodiments, a software module (or program module) comes in
the form of one or more files and typically handles a specific task
within a larger software system.
In some embodiments, a module is included in one or more software
systems. In other embodiments, a module is integrated with one or
more other modules into one or more software systems. A computer
module is optionally a stand-alone section of code or, optionally,
code that is not separately identifiable. In some embodiments, the
modules are in a single application. In other embodiments, the
modules are in a plurality of applications. In some embodiments,
the modules are hosted on one machine. In other embodiments, the
modules are hosted on a plurality of machines. In some embodiments,
the modules are hosted on a plurality of machines in one location.
In other embodiments, the modules are hosted a plurality of
machines in more than one location. Further described herein is the
formatting of location and positioning data. In some embodiments,
the data files described herein are formatted in any suitable data
serialization format including, by way of non-limiting examples,
tab-separated values, comma-separated values, character-separated
values, delimiter-separated values, XML, JSON, B SON, and YAML. A
key feature of a computer module is that it allows an end user to
use a computer to perform the identified functions.
Graphic User Interface
In some embodiments, a computer module comprises a graphic user
interface (GUI). As used herein, "graphic user interface" means a
user environment that uses pictorial as well as textual
representations of the input and output of applications and the
hierarchical or other data structure in which information is
stored. In some embodiments, a computer module comprises a display
screen. In further embodiments, a computer module presents, via a
display screen, a two-dimensional GUI. In other embodiments, a
computer module presents, via a display screen, a three-dimensional
GUI such as a virtual reality environment. In some embodiments, the
display screen is a touchscreen or multitouchscreen and presents an
interactive GUI.
In some embodiments, the display screen presents a GUI that
consists essentially of a grid comprising regularly spaced objects
of substantially the same shape and substantially equal size. The
objects presented have any suitable shape. In some embodiments,
suitable shapes for objects include, by way of non-limiting
examples, circle, oval, square, rectangle, triangle, diamond,
polygon, or a combination thereof.
In some embodiments, a user defines the content of one or more
objects to form a two-dimensional or three-dimensional visual
representation of a desired tissue construct. See, e.g., FIG. 4. In
some embodiments, the user-defined content of an object is, by way
of non-limiting examples, a bio-ink with various compositions or
support material with various compositions. In some embodiments,
the user defines the content of an object by modifying the color of
the cell or the shape of the object.
Bio-Ink
Disclosed herein, in certain embodiments, are devices, systems, and
methods for fabricating tissues and organs. In some embodiments,
the devices comprise one or more printer heads for receiving and
holding at least one cartridge that optionally contains bio-ink. In
some embodiments, the methods comprise the use of bio-ink. In
further embodiments, the tissues and organs fabricated by use of
the devices, systems, and methods described herein comprise bio-ink
at the time of fabrication or thereafter.
In some embodiments, "bio-ink" includes liquid, semi-solid, or
solid compositions comprising a plurality of cells. In some
embodiments, bio-ink comprises liquid or semi-solid cell solutions,
cell suspensions, or cell concentrations. In further embodiments, a
cell solution, suspension, or concentration comprises a liquid or
semi-solid (e.g., viscous) carrier and a plurality of cells. In
still further embodiments, the carrier is a suitable cell nutrient
media, such as those described herein. In some embodiments, bio-ink
comprises semi-solid or solid multicellular aggregates or
multicellular bodies. In further embodiments, the bio-ink is
produced by 1) mixing a plurality of cells or cell aggregates and a
biocompatible liquid or gel in a pre-determined ratio to result in
bio-ink, and 2) compacting the bio-ink to produce the bio-ink with
a desired cell density and viscosity. In some embodiments, the
compacting of the bio-ink is achieved by centrifugation, tangential
flow filtration ("TFF"), or a combination thereof. In some
embodiments, the compacting of the bio-ink results in a composition
that is extrudable, allowing formation of multicellular aggregates
or multicellular bodies. In some embodiments, "extrudable" means
able to be shaped by forcing (e.g., under pressure) through a
nozzle or orifice (e.g., one or more holes or tubes). In some
embodiments, the compacting of the bio-ink results from growing the
cells to a suitable density. The cell density necessary for the
bio-ink will vary with the cells being used and the tissue or organ
being produced. In some embodiments, the cells of the bio-ink are
cohered and/or adhered. In some embodiments, "cohere," "cohered,"
and "cohesion" refer to cell-cell adhesion properties that bind
cells, multicellular aggregates, multicellular bodies, and/or
layers thereof. In further embodiments, the terms are used
interchangeably with "fuse," "fused," and "fusion." In some
embodiments, the bio-ink additionally comprises support material,
cell culture medium, extracellular matrix (or components thereof),
cell adhesion agents, cell death inhibitors, anti-apoptotic agents,
anti-oxidants, extrusion compounds, and combinations thereof.
Cells
Disclosed herein, in various embodiments, are bio-inks that include
liquid, semi-solid, or solid compositions comprising a plurality of
cells. In some embodiments, bio-ink comprises liquid or semi-solid
cell solutions, cell suspensions, or cell concentrations. In some
embodiments, any mammalian cell is suitable for use in bio-ink and
in the fabrication of tissues and organs using the devices,
systems, and methods described herein. In various embodiments, the
cells are any suitable cell. In further various embodiments, the
cells are vertebrate cells, mammalian cells, human cells, or
combinations thereof. In some embodiments, the type of cell used in
a method disclosed herein depends on the type of cellular
construct, tissue, or organ being produced. In some embodiments,
the bio-ink comprises one type of cell (also referred to as a
"homologous ink"). In some embodiments, the bio-ink comprises more
than one type of cell (also referred to as a "heterologous
ink").
In further embodiments, the cells are, by way of non-limiting
examples, contractile or muscle cells (e.g., skeletal muscle cells,
cardiomyocytes, smooth muscle cells, and myoblasts), connective
tissue cells (e.g., bone cells, cartilage cells, fibroblasts, and
cells differentiating into bone forming cells, chondrocytes, or
lymph tissues), bone marrow cells, endothelial cells, skin cells,
epithelial cells, breast cells, vascular cells, blood cells, lymph
cells, neural cells, Schwann cells, gastrointestinal cells, liver
cells, pancreatic cells, lung cells, tracheal cells, corneal cells,
genitourinary cells, kidney cells, reproductive cells, adipose
cells, parenchymal cells, pericytes, mesothelial cells, stromal
cells, undifferentiated cells (e.g., embryonic cells, stem cells,
and progenitor cells), endoderm-derived cells, mesoderm-derived
cells, ectoderm-derived cells, and combinations thereof.
In some embodiments, the cells are adult, differentiated cells. In
further embodiments, "differentiated cells" are cells with a
tissue-specific phenotype consistent with, for example, a smooth
muscle cell, a fibroblast, or an endothelial cell at the time of
isolation, wherein tissue-specific phenotype (or the potential to
display the phenotype) is maintained from the time of isolation to
the time of use. In other embodiments, the cells are adult,
non-differentiated cells. In further embodiments,
"non-differentiated cells" are cells that do not have, or have
lost, the definitive tissue-specific traits of for example, smooth
muscle cells, fibroblasts, or endothelial cells. In some
embodiments, non-differentiated cells include stem cells. In
further embodiments, "stem cells" are cells that exhibit potency
and self-renewal. Stem cells include, but are not limited to,
totipotent cells, pluripotent cells, multipotent cells, oligopotent
cells, unipotent cells, and progenitor cells. Stem cells may be
embryonic stem cells, adult stem cells, amniotic stem cells, and
induced pluripotent stem cells. In yet other embodiments, the cells
are a mixture of adult, differentiated cells and adult,
non-differentiated cells.
Cell Culture Media
In some embodiments, the bio-ink comprises a cell culture medium.
The cell culture medium is any suitable medium. In various
embodiments, suitable cell culture media include, by way of
non-limiting examples, Dulbecco's Phosphate Buffered Saline,
Earle's Balanced Salts, Hanks' Balanced Salts, Tyrode's Salts,
Alsever's Solution, Gey's Balanced Salt Solution, Kreb's-Henseleit
Buffer Modified, Kreb's-Ringer Bicarbonate Buffer, Puck's Saline,
Dulbecco's Modified Eagle's Medium, Dulbecco's Modified Eagle's
Medium/Nutrient F-12 Ham, Nutrient Mixture F-10 Ham (Ham's F-10),
Medium 199, Minimum Essential Medium Eagle, RPMI-1640 Medium, Ames'
Media, BGJb Medium (Fitton-Jackson Modification), Click's Medium,
CMRL-1066 Medium, Fischer's Medium, Glascow Minimum Essential
Medium (GMEM), Iscove's Modified Dulbecco's Medium (IMDM), L-15
Medium (Leibovitz), McCoy's 5A Modified Medium, NCTC Medium, Swim's
S-77 Medium, Waymouth Medium, William's Medium E, or combinations
thereof. In some embodiments, the cell culture medium is modified
or supplemented. In some embodiments, the cell culture medium
further comprises albumin, selenium, transferrins, fetuins, sugars,
amino acids, vitamins, growth factors, cytokines, hormones,
antibiotics, lipids, lipid carriers, cyclodextrins, or a
combination thereof.
Extracellular Matrix
In some embodiments, the bio-ink further comprises one or more
components of an extracellular matrix or derivatives thereof. In
some embodiments, "extracellular matrix" includes proteins that are
produced by cells and transported out of the cells into the
extracellular space, where they may serve as a support to hold
tissues together, to provide tensile strength, and/or to facilitate
cell signaling. Examples, of extracellular matrix components
include, but are not limited to, collagen, fibronectin, laminin,
hyaluronates, elastin, and proteoglycans. For example,
multicellular aggregates may contain various ECM proteins (e.g.,
gelatin, fibrinogen, fibrin, collagen, fibronectin, laminin,
elastin, and/or proteoglycans). The ECM components or derivatives
of ECM components can be added to the cell paste used to form the
multicellular aggregate. The ECM components or derivatives of ECM
components added to the cell paste can be purified from a human or
animal source, or produced by recombinant methods known in the art.
Alternatively, the ECM components or derivatives of ECM components
can be naturally secreted by the cells in the elongate cellular
body, or the cells used to make the elongate cellular body can be
genetically manipulated by any suitable method known in the art to
vary the expression level of one or more ECM components or
derivatives of ECM components and/or one or more cell adhesion
molecules or cell-substrate adhesion molecules (e.g., selectins,
integrins, immunoglobulins, and adherins). The ECM components or
derivatives of ECM components may promote cohesion of the cells in
the multicellular aggregates. For example, gelatin and/or
fibrinogen can suitably be added to the cell paste, which is used
to form multicellular aggregates. The fibrinogen can then be
converted to fibrin by the addition of thrombin.
In some embodiments, the bio-ink further comprises an agent that
encourages cell adhesion.
In some embodiments, the bio-ink further comprises an agent that
inhibits cell death (e.g., necrosis, apoptosis, or
autophagocytosis). In some embodiments, the bio-ink further
comprises an anti-apoptotic agent. Agents that inhibit cell death
include, but are not limited to, small molecules, antibodies,
peptides, peptibodies, or combination thereof. In some embodiments,
the agent that inhibits cell death is selected from: anti-TNF
agents, agents that inhibit the activity of an interleukin, agents
that inhibit the activity of an interferon, agents that inhibit the
activity of an GCSF (granulocyte colony-stimulating factor), agents
that inhibit the activity of a macrophage inflammatory protein,
agents that inhibit the activity of TGF-B (transforming growth
factor B), agents that inhibit the activity of an MMP (matrix
metalloproteinase), agents that inhibit the activity of a caspase,
agents that inhibit the activity of the MAPK/JNK signaling cascade,
agents that inhibit the activity of a Src kinase, agents that
inhibit the activity of a JAK (Janus kinase), or a combination
thereof. In some embodiments, the bio-ink comprises an
anti-oxidant.
Extrusion Compounds
In some embodiments, the bio-ink further comprises an extrusion
compound (i.e., a compound that modifies the extrusion properties
of the bio-ink). Examples of extrusion compounds include, but are
not limited to gels, hydrogels, surfactant polyols (e.g., Pluronic
F-127 or PF-127), thermo-responsive polymers, hyaluronates,
alginates, extracellular matrix components (and derivatives
thereof), collagens, other biocompatible natural or synthetic
polymers, nanofibers, and self-assembling nanofibers.
Gels, sometimes referred to as jellies, have been defined in
various ways. For example, the United States Pharmacopoeia defines
gels as semisolid systems consisting of either suspensions made up
of small inorganic particles or large organic molecules
interpenetrated by a liquid. Gels include a single-phase or a
two-phase system. A single-phase gel consists of organic
macromolecules distributed uniformly throughout a liquid in such a
manner that no apparent boundaries exist between the dispersed
macromolecules and the liquid. Some single-phase gels are prepared
from synthetic macromolecules (e.g., carbomer) or from natural gums
(e.g., tragacanth). In some embodiments, single-phase gels are
generally aqueous, but will also be made using alcohols and oils.
Two-phase gels consist of a network of small discrete
particles.
Gels can also be classified as being hydrophobic or hydrophilic. In
certain embodiments, the base of a hydrophobic gel consists of a
liquid paraffin with polyethylene or fatty oils gelled with
colloidal silica, or aluminum or zinc soaps. In contrast, the base
of hydrophobic gels usually consists of water, glycerol, or
propylene glycol gelled with a suitable gelling agent (e.g.,
tragacanth, starch, cellulose derivatives, carboxyvinylpolymers,
and magnesium-aluminum silicates). In certain embodiments, the
rheology of the compositions or devices disclosed herein is pseudo
plastic, plastic, thixotropic, or dilatant.
Suitable hydrogels include those derived from collagen,
hyaluronate, fibrin, alginate, agarose, chitosan, and combinations
thereof. In other embodiments, suitable hydrogels are synthetic
polymers. In further embodiments, suitable hydrogels include those
derived from poly(acrylic acid) and derivatives thereof,
poly(ethylene oxide) and copolymers thereof, poly(vinyl alcohol),
polyphosphazene, and combinations thereof. In various specific
embodiments, the support material is selected from: hydrogel,
NovoGel.TM., agarose, alginate, gelatin, Matrigel.TM., hyaluronan,
poloxamer, peptide hydrogel, poly(isopropyl n-polyacrylamide),
polyethylene glycol diacrylate (PEG-DA), hydroxyethyl methacrylate,
polydimethylsiloxane, polyacrylamide, poly(lactic acid), silicon,
silk, or combinations thereof.
In some embodiments, hydrogel-based extrusion compounds are
thermoreversible gels (also known as thermo-responsive gels or
thermogels). In some embodiments, a suitable thermoreversible
hydrogel is not a liquid at room temperature. In specific
embodiments, the gelation temperature (Tgel) of a suitable hydrogel
is about 10.degree. C., about 15.degree. C., about 20.degree. C.,
about 25.degree. C., about 30.degree. C., about 35.degree. C., and
about 40.degree. C., including increments therein. In certain
embodiments, the Tgel of a suitable hydrogel is about 10.degree. C.
to about 25.degree. C. In some embodiments, the bio-ink (e.g.,
comprising hydrogel, one or more cell types, and other additives,
etc.) described herein is not a liquid at room temperature. In
specific embodiments, the gelation temperature (Tgel) of a bio-ink
described herein is about 10.degree. C., about 15.degree. C., about
20.degree. C., about 25.degree. C., about 30.degree. C., about
35.degree. C., and about 40.degree. C., including increments
therein. In certain embodiments, the Tgel of a bio-ink described
herein is about 10.degree. C. to about 25.degree. C.
Polymers composed of polyoxypropylene and polyoxyethylene form
thermoreversible gels when incorporated into aqueous solutions.
These polymers have the ability to change from the liquid state to
the gel state at temperatures that can be maintained in a
bioprinter apparatus. The liquid state-to-gel state phase
transition is dependent on the polymer concentration and the
ingredients in the solution.
Poloxamer 407 (Pluronic F-127 or PF-127) is a nonionic surfactant
composed of polyoxyethylene-polyoxypropylene copolymers. Other
poloxamers include 188 (F-68 grade), 237 (F-87 grade), 338 (F-108
grade). Aqueous solutions of poloxamers are stable in the presence
of acids, alkalis, and metal ions. PF-127 is a commercially
available polyoxyethylene-polyoxypropylene triblock copolymer of
general formula E106 P70 E106, with an average molar mass of
13,000. The polymer can be further purified by suitable methods
that will enhance gelation properties of the polymer. It contains
approximately 70% ethylene oxide, which accounts for its
hydrophilicity. It is one of the series of poloxamer ABA block
copolymers. PF-127 has good solubilizing capacity, low toxicity and
is, therefore, considered a suitable extrusion compound.
In some embodiments, the viscosity of the hydrogels and bio-inks
presented herein is measured by any means described. For example,
in some embodiments, an LVDV-II+CP Cone Plate Viscometer and a Cone
Spindle CPE-40 is used to calculate the viscosity of the hydrogels
and bio-inks. In other embodiments, a Brookfield (spindle and cup)
viscometer is used to calculate the viscosity of the hydrogels and
bio-inks. In some embodiments, the viscosity ranges referred to
herein are measured at room temperature. In other embodiments, the
viscosity ranges referred to herein are measured at body
temperature (e.g., at the average body temperature of a healthy
human).
In further embodiments, the hydrogels and/or bio-inks are
characterized by having a viscosity of between about 500 and
1,000,000 centipoise, between about 750 and 1,000,000 centipoise;
between about 1000 and 1,000,000 centipoise; between about 1000 and
400,000 centipoise; between about 2000 and 100,000 centipoise;
between about 3000 and 50,000 centipoise; between about 4000 and
25,000 centipoise; between about 5000 and 20,000 centipoise; or
between about 6000 and 15,000 centipoise.
In some embodiments, the bio-ink comprises cells and extrusion
compounds suitable for continuous bioprinting. In specific
embodiments, the bio-ink has a viscosity of about 1500 mPas. A
mixture of Pluronic F-127 and cellular material may be suitable for
continuous bioprinting. Such a bio-ink may be prepared by
dissolving Pluronic F-127 powder by continuous mixing in cold
(4.degree. C.) phosphate buffered saline (PBS) over 48 hours to 30%
(w/v). Pluronic F-127 may also be dissolved in water. Cells may be
cultivated and expanded using standard sterile cell culture
techniques. The cells may be pelleted at 200 g for example, and
re-suspended in the 30% Pluronic F-127 and aspirated into a
reservoir affixed to a bioprinter where it can be allowed to
solidify at a gelation temperature from about 10 to about
25.degree. C. Gelation of the bio-ink prior to bioprinting is
optional. The bio-ink, including bio-ink comprising Pluronic F-127
can be dispensed as a liquid.
In various embodiments, the concentration of Pluronic F-127 can be
any value with suitable viscosity and/or cytotoxicity properties. A
suitable concentration of Pluronic F-127 may also be able to
support weight while retaining its shape when bioprinted. In some
embodiments, the concentration of Pluronic F-127 is about 10%,
about 15%, about 20%, about 25%, about 30%, about 35%, about 40%,
about 45%, or about 50%. In some embodiments, the concentration of
Pluronic F-127 is between about 30% and about 40%, or between about
30% and about 35%.
FIG. 5 depicts a three-dimensional, pyramid-shaped construct
generated by continuous deposition of PF-127 using a NovoGen
MMX.TM. bioprinter connected to a syringe with a 510 .mu.m
needle.
FIG. 6 depicts a three-dimensional, cube-shaped (left) and hollow
cube-shaped (right) constructs generated by continuous deposition
of PF-127 using a NovoGen MMX.TM. bioprinter connected to a syringe
with a 510 .mu.m needle.
In some embodiments, the non-cellular components of the bio-ink
(e.g., extrusion compounds, etc.) are removed prior to use. In
further embodiments, the non-cellular components are, for example,
hydrogels, surfactant polyols, thermo-responsive polymers,
hyaluronates, alginates, collagens, or other biocompatible natural
or synthetic polymers. In still further embodiments, the
non-cellular components are removed by physical, chemical, or
enzymatic means. In some embodiments, a proportion of the
non-cellular components remain associated with the cellular
components at the time of use.
In some embodiments, the cells are pre-treated to increase cellular
interaction. For example, cells may be incubated inside a
centrifuge tube after centrifugation in order to enhance cell-cell
interactions prior to shaping the bio-ink.
Support Material
Disclosed herein, in certain embodiments, are devices, systems, and
methods for fabricating tissues and organs. In some embodiments,
the devices comprise one or more printer heads for receiving and
holding at least one cartridge that optionally contains support
material. In some embodiments, the methods comprise the use of
support material. In further embodiments, the tissues and organs
fabricated by use of the devices, systems, and methods described
herein comprise support material at the time of fabrication or
thereafter.
In some embodiments, the support material is capable of excluding
cells growing or migrating into or adhering to it. In some
embodiments, the support material is permeable for nutrient
media.
In some embodiments, the viscosity of the support material is
changeable. In some embodiments, the viscosity of the support
material is changed by modifying the temperature of the support
material. In some embodiments, the viscosity of the support
material is changed by modifying the pressure of the support
material. In some embodiments, the viscosity of the support
material is changed by modifying the concentration of the support
material. In some embodiments, the viscosity of the support
material is changed by crosslinking (e.g., by use of a chemical
cross-linker), or photocrossinking (e.g., using ultraviolet light
exposure).
In some embodiments, the permeability of the support material is
changeable. In some embodiments, the permeability of the support
material is modified by varying the temperature of the support
material or the temperature surrounding the support material. In
some embodiments, the permeability of the support material is
modified by contacting the support material with an agent that
modifies permeability.
In some embodiments, the compliance (i.e., elasticity or hardness)
of the support material is modified. In some embodiments, the
compliance of the support material is modified by varying the
temperature of the support material or the temperature surrounding
the support material. In some embodiments, the compliance of the
support material is modified by contacting the support material
with an agent that modifies compliance.
Many support materials are suitable for use in the methods
described herein. In some embodiments, hydrogels are exemplary
support materials possessing one or more advantageous properties
including: non-adherent, biocompatible, extrudable, bioprintable,
non-cellular, and of suitable strength. In some embodiments,
suitable hydrogels are natural polymers. In one embodiment, the
confinement material is comprised of NovoGel.TM.. In further
embodiments, suitable hydrogels include those derived from
surfactant polyols (e.g., Pluronic F-127), collagen, hyaluronate,
fibrin, alginate, agarose, chitosan, derivatives or combinations
thereof. In other embodiments, suitable hydrogels are synthetic
polymers. In further embodiments, suitable hydrogels include those
derived from poly(acrylic acid) and derivatives thereof,
poly(ethylene oxide) and copolymers thereof, poly(vinyl alcohol),
polyphosphazene, and combinations thereof. In various specific
embodiments, the confinement material is selected from: hydrogel,
NovoGel.TM., agarose, alginate, gelatin, Matrigel.TM., hyaluronan,
poloxamer, peptide hydrogel, poly(isopropyl n-polyacrylamide),
polyethylene glycol diacrylate (PEG-DA), hydroxyethyl methacrylate,
polydimethylsiloxane, polyacrylamide, poly(lactic acid), silicon,
silk, or combinations thereof.
In some embodiments, the support material contains cells prior to
being present in the bioprinter. In some embodiments, the support
material is a hydrogel containing a suspension of cells. In some
embodiments, the support material is a hydrogel containing a
mixture of more than one cell type.
Exemplary Uses of Support Materials
In some embodiments, the support material is used as building units
for constructing a biological construct (e.g., cellular construct,
tissue, organ, etc.). In further embodiments, the support material
unit is used to define and maintain the domains void of cellular
material (i.e., the intermediate cellular units) of a desired
construct. In some embodiments, the support material is capable of
assuming any shape or size.
For example, according to one embodiment, NovoGel.TM. solution
(originally in powder phase mixed with buffer and water) may be
heated to reduce its viscosity and taken up in a micropipette with
a desired dimension (or in a chamber of a desired shape by negative
displacement of a piston). The NovoGel.TM. solution in the pipette
(or the chamber) may be cooled to room temperature, for example by
forced air on the exterior of the pipette (or the chamber) or
plunging the micropipette into a container with cold liquid, so
that it can solidify into a gel with the desired shape, i.e., a
support material. The resulting support material may be dispensed
from the pipette or chamber during the construction of a particular
cellular construct, tissue, or organ. See e.g., FIG. 4.
In some embodiments, the support material is used for increasing
the viability of the engineered tissue or organ after bioprinting.
In further embodiments, support material provides direct contact
between the tissue or organ and a nutrient medium through a
temporary or semi-permanent lattice of confinement material (e.g.,
support material). In some embodiments, the tissue is constrained
in a porous or gapped material. Direct access of at least some of
the cells of the tissue or organ to nutrients increases the
viability of the tissue or organ.
In further embodiments, the methods disclosed herein comprise
additional and optional steps for increasing the viability of an
engineered tissue or organ including: 1) optionally dispensing base
layer of confinement material (e.g., support material) prior to
placing cohered multicellular aggregates; 2) optionally dispensing
a perimeter of confinement material; 3) bioprinting cells of the
tissue within a defined geometry; and 4) dispensing elongate bodies
(e.g., cylinders, ribbons, etc.) of confinement material overlaying
the nascent tissue in a pattern that introduces gaps in the
confinement material, such as a lattice, mesh, or grid.
In some embodiments, the gaps overlaying pattern are distributed
uniformly or substantially uniformly around the surface of the
tissue or organ. In other embodiments, the gaps are distributed
non-uniformly, whereby the cells of the tissue or organ are exposed
to nutrients non-uniformly. In non-uniform embodiments, the
differential access to nutrients may be exploited to influence one
or more properties of the tissue or organ. For instance, it may be
desirable to have cells on one surface of a bioprinted, cellular
construct, tissue, or organ proliferate faster than cells on
another surface. In some embodiments, the exposure of various parts
of the tissue or organ to nutrients can be changed at various times
to influence the development of the tissue or organ toward a
desired endpoint.
In some embodiments, the confinement material is removed at any
suitable time, including but not limited to, immediately after
bioprinting (e.g., within 10 minutes), after bioprinting (e.g.,
after 10 minutes), before the cells are substantially cohered to
each other, after the cells are substantially cohered to each
other, before the cells produce an extracellular matrix, after the
cells produce an extracellular matrix, just prior to use, and the
like. In various embodiments, confinement material is removed by
any suitable method. For example, in some embodiments, the
confinement material is excised, pulled off the cells, digested, or
dissolved.
Methods and Systems for Calibrating the Position of a Bioprinter
Cartridge
Disclosed herein, in certain embodiments, are bioprinters for
fabricating tissues and organs. In some embodiments, a cartridge
attached to the bioprinter comprises a bio-ink and/or a support
material. In some embodiments, the bioprinter deposits the bio-ink
or support material in a specific pattern and at specific positions
in order to form a specific tissue construct. In some embodiments,
a cartridge comprising bio-ink is disposable. In some embodiments,
the cartridge is ejected from the bioprinter following extrusion,
dispensing, or deposition of the contents. In some embodiments, a
new cartridge is attached to the bioprinter.
In order to fabricate complex structures, the bioprinters disclosed
herein dispense bio-ink and/or support material from a cartridge
with a suitable repeatable accuracy. In various embodiments,
suitable repeatable accuracies include those of about .+-.5, 10,
20, 30, 40, or 50 .mu.m on any axis. In some embodiments, the
bioprinters disclosed herein dispense bio-ink and/or support
material from a cartridge with a repeatable accuracy of about
.+-.20 .mu.m. However, in some embodiments, due to the removal and
insertion of cartridges, the position of the printer head (and thus
the cartridges) with respect to the tissue construct varies. Thus,
there is a need for a method of precisely calibrating the position
of the printer head, cartridge, and dispensing orifice with respect
to the printer stage, receiving surface, tissue, or organ.
In some embodiments, the method of calibrating the position of a
printer head comprises use of at least one laser. In further
embodiments, the method of calibrating the position of a printer
head comprises use of a first and second laser.
In some embodiments, the method of calibrating the position of a
printer head comprises manual (e.g., visual) calibration.
In some embodiments, the method of calibrating the position of a
printer head comprises manual calibration and laser
calibration.
In some embodiments, the position of the printer head is calibrated
along one axis, wherein the axis is selected from the x-axis, the
y-axis, and the z-axis. In some embodiments, the position of the
printer head is calibrated along two axes, wherein the axes are
selected from the x-axis, the y-axis, and the z-axis. In some
embodiments, the position of the printer head is calibrated along
three axes, wherein the axes are selected from the x-axis, the
y-axis, and the z-axis.
In some embodiments, calibration is made by use of at least one
laser. In further embodiments, calibration is made by use of a
first and a second laser.
Method for Calibrating Using a Horizontal Laser
Disclosed herein, in certain embodiments, are methods of
calibrating the position of a printer head comprising a dispensing
orifice. In some embodiments, a method disclosed herein further
comprises activating a laser and generating at least one
substantially stable and/or substantially stationary laser beam,
and where said laser beam is horizontal to the ground. See FIG.
1.
In some embodiments, the methods comprise, calibrating the position
of a printer head along at least one axis, wherein the axis is
selected from the x-axis, y-axis, and z-axis. In some embodiments,
the methods comprise calibrating the position of the printer head
along at least two axes, wherein the axis is selected from the
x-axis, y-axis, and z-axis. In some embodiments, the methods
comprise calibrating the position of the printer head along at
least three axes, wherein the axis is selected from the x-axis,
y-axis, and z-axis. In some embodiments, the methods comprise (a)
calibrating the position of the printer head along the y-axis; (b)
calibrating the position of the printer head along the x-axis;
and/or (c) calibrating the position of the printer head along the
z-axis; wherein each axis corresponds to the axis of the same name
in the Cartesian coordinate system. In some embodiments,
calibration is made by use of at least one laser. In some
embodiments, calibration is made by use of a first and a second
laser.
In some embodiments, calibrating the position of a printer head
along the y-axis comprises: (a) positioning the printer head so
that the printer head is (i) located in a first y octant and (ii)
the dispensing orifice is below the upper threshold of the laser
beam; (b) moving the printer head towards the laser beam and
stopping said movement as soon as the laser beam is interrupted by
the printer head, wherein the position at which the laser beam is
interrupted by the printer head is the first y position; (c)
re-positioning the printer head so that the printer head is located
in the second y octant and the dispensing orifice is below the
upper threshold of the laser beam; (d) moving the printer head
towards the laser beam and stopping said movement as soon as the
laser beam is interrupted by the printer head, wherein the position
at which the laser beam is interrupted is the second y position;
(e) and calculating the mid-point between the first y position and
the second y position.
In some embodiments, calibrating the position of a printer head
along the x-axis comprises: (a) positioning the printer head (i) at
the mid-point between the first y position and the second y
position, and (ii) outside the sensor threshold of the laser; and
(b) moving the printer head towards the sensor threshold and
stopping said movement as soon as the printer head contacts the
sensor threshold; wherein the position at which the printer head
contacts the sensor increased by half the printer head width is the
x position.
In some embodiments, calibrating the position of a printer head
along the y-axis comprises: (a) positioning the printer head so
that the laser beam can measure the precise location of one side of
the printer head; (b) positioning the printer head so that the
laser beam can measure the precise location of the opposing side of
the printer head; (c) and calculating the midpoint location of the
printer head to be relative to the laser location during each
measurement and the measured distances.
In some embodiments, calibrating the position of a printer head
along the x-axis comprises: (a) positioning the printer head so
that the laser beam can measure the precise location of one side of
the printer head; (b) positioning the printer head so that the
laser beam can measure the precise location of the opposing side of
the printer head; (c) and calculating the midpoint location of the
printer head to be relative to the laser location during each
measurement and the measured distances.
In some embodiments, calibrating the position of a printer head
along the z-axis comprises: (a) positioning the printer head so
that the dispensing orifice is located above the laser beam; and
(b) moving the printer head towards the laser beam and stopping
said movement as soon as the laser beam is interrupted by the
printer head, wherein the position at which the laser beam is
interrupted is the z position.
Method for Calibrating Using a Vertical Laser
Disclosed herein, in certain embodiments, are methods of
calibrating the position of a printer head comprising a dispensing
orifice. In some embodiments, a method disclosed herein further
comprises activating the laser and generating at least one
substantially stable and/or substantially stationary laser beam,
and where said laser beam is vertical to the ground. See FIG.
2.
In some embodiments, the methods comprise, calibrating the position
of a printer head along at least one axis, wherein the axis is
selected from the x-axis, y-axis, and z-axis. In some embodiments,
the methods comprise calibrating the position of a printer head
along at least two axes, wherein the axis is selected from the
x-axis, y-axis, and z-axis. In some embodiments, the methods
comprise calibrating the position of a printer head along at least
three axes, wherein the axis is selected from the x-axis, y-axis,
and z-axis.
In some embodiments, the methods comprise (a) calibrating the
position of the printer head along the y-axis; (b) calibrating the
position of the printer head along the x-axis; and (c) calibrating
the position of the printer head along the z-axis; wherein each
axis corresponds to the axis of the same name in the Cartesian
coordinate system.
In some embodiments, calibrating the position of a printer head
along the y-axis comprises: (a) positioning the printer head so
that the printer head is (i) located in a first y octant and (ii)
the dispensing orifice is outside the sensor threshold of the
laser; (b) moving the printer head towards the laser beam and
stopping said movement as soon as the laser beam is interrupted by
the printer head, wherein the position at which the laser beam is
interrupted by the printer head is the first y position; (c)
re-positioning the printer head so that the printer head is located
in the second y octant and the dispensing orifice is outside the
sensor threshold of the laser; (d) moving the printer head towards
the laser beam and stopping said movement as soon as the laser beam
is interrupted by the printer head, wherein the position at which
the laser beam is interrupted is the second y position; (e) and
calculating the mid-point between the first y position and the
second y position.
In some embodiments, calibrating the position of a printer head
along the x-axis comprises: (a) positioning the printer head (i) at
the mid-point between the first y position and the second y
position, and (ii) outside the sensor threshold of the laser; and
(b) moving the printer head towards the sensor threshold and
stopping said movement as soon as the printer head contacts the
sensor threshold; wherein the position at which the printer head
contacts the sensor increased by half the printer head width is the
x position.
In some embodiments, calibrating the position of a printer head
along the z-axis comprises: (a) positioning the printer head so
that the dispensing orifice is located above the laser beam so that
it is just outside of the laser sensor range threshold; and (b)
lowering the printer head until the sensor threshold is reached,
wherein the position at which the laser sensor threshold is reached
is the z position. In some embodiments, steps (a) and (b) are
repeated at multiple points of the printer head and measured
heights are averaged to determine the z position.
In some embodiments, calibrating the position of a printer head
along the z-axis comprises: (a) positioning the printer head so
that the laser beam can measure the precise location of one or more
points on the bottom of the printer head; (b) calculating the
absolute or average location of the printer head based on the laser
position and known measured distance.
Method for Calibrating Using a Vertical and Horizontal Laser
Disclosed herein, in certain embodiments, are methods of
calibrating the position of a printer head comprising a dispensing
orifice, wherein the printer head is attached to a bioprinter,
comprising calibrating the position of the printer head along at
least one axis, wherein the axis is selected from the x-axis,
y-axis, and z-axis. In some embodiments, the method comprises
calibrating the position of a printer head along at least two axes,
wherein the axis is selected from the x-axis, y-axis, and z-axis.
In some embodiments, the method comprises calibrating the position
of a printer head along at least three axes, wherein the axis is
selected from the x-axis, y-axis, and z-axis.
In some embodiments, the methods comprise (a) calibrating the
position of the printer head along the y-axis; (b) calibrating the
position of the printer head along the x-axis; and (c) calibrating
the position of the printer head along the z-axis; wherein each
axis corresponds to the axis of the same name in the Cartesian
coordinate system.
In some embodiments, calibration comprises use of a first laser and
a second laser. In some embodiments, the first laser is a vertical
laser and the second laser is a horizontal laser.
System for Calibrating Using a Laser
Disclosed herein, in certain embodiments, are systems for
calibrating the position of a cartridge comprising a deposition
orifice, wherein the cartridge is attached to a bioprinter, said
system comprising: a means for calibrating the position of the
cartridge along at least one axis, wherein the axis is selected
from the y-axis, x-axis, and z-axis.
Also disclosed herein, in certain embodiments, are systems for
calibrating the position of a printer head comprising a dispensing
orifice, wherein the printer head is attached to a bioprinter, said
system comprising: a means for calibrating the position of the
printer head along an x-axis; a means for calibrating the position
of the printer head along a y-axis; and a means for calibrating the
position of the printer head along a z-axis.
In some embodiments, a system for calibrating the position of a
printer head comprises a means for calibrating the printer head
along the x-axis, y-axis, and z-axis. In some embodiments, the
means for calibrating a printer head along the x-axis, y-axis, and
z-axis is laser alignment, optical alignment, mechanical alignment,
piezoelectric alignment, magnetic alignment, electrical field or
capacitance alignment, ultrasound alignment, or a combination
thereof.
In some embodiments, a system for calibrating the position of a
printer head comprises a means for calibrating the printer head
along the x-axis, y-axis, and z-axis. In some embodiments, the
means for calibrating a printer head along the x-axis, y-axis, and
z-axis is laser alignment. In some embodiments, the laser alignment
means comprises at least one laser. In some embodiments, the laser
alignment means comprises a plurality of lasers.
In some embodiments, the laser alignment means it has any suitable
accuracy. In various embodiments, suitable accuracies include those
of about .+-.5, 10, 20, 30, 40, or 50 .mu.m on any axis. In some
embodiments, the laser alignment means is accurate to .+-.40 .mu.m
on the vertical axis and .+-.20 .mu.m on the horizontal axis.
In some embodiments, the laser path is uninterrupted between the
laser source and the measurement point. In some embodiments, the
laser path is altered by up to 179.degree. by use of a reflective
surface or optical lens. In some embodiments, the laser path is
altered by 90.degree.. In some embodiments, a horizontal laser beam
is used to measure in a vertical path by deflection using a
reflective surface. In some embodiments, a vertical laser beam is
used to measure in a horizontal path by deflection using a
reflective surface.
EXAMPLES
The following specific examples are to be construed as merely
illustrative, and not limitative of the remainder of the disclosure
in any way whatsoever. Without further elaboration, it is believed
that one skilled in the art can, based on the description herein,
utilize the present invention to its fullest extent. All
publications cited herein are hereby incorporated by reference in
their entirety. Reference thereto evidences the availability and
public dissemination of such information.
Example 1: HASMC-HAEC Mixed Cellular Cylinders
Cell Culture
Smooth muscle cells: Primary human aortic smooth muscle cells
(HASMC) were maintained and expanded in low glucose Dulbecco's
modified eagle medium (DMEM; Invitrogen Corp., Carlsbad, Calif.)
supplemented with 10% fetal bovine serum (FBS), 100 U/ml
Penicillin, 0.1 mg/ml streptomycin, 0.25 .mu.g/ml of amphotericin
B, 0.01M of HEPES (all from Invitrogen Corp., Carlsbad, Calif.), 50
mg/L of proline, 50 mg/L of glycine, 20 mg/L of alanine, 50 mg/L of
ascorbic acid, and 3 .mu.g/L of CuSO.sub.4 (all from Sigma, St.
Louis, Mo.) at 37.degree. C. and 5% CO.sub.2. Confluent cultures of
HASMCs between passage 4 and 8 were used in all studies.
Endothelial cells: Primary human aortic endothelial cells (HAEC)
were maintained and expanded in Medium 200 supplemented with 2%
FBS, 1 .mu.g/ml of hydrocortisone, 10 ng/ml of human epidermal
growth factor, 3 ng/ml of basic fibroblast growth factor, 10
.mu.g/ml of heparin, 100 U/ml Penicillin, 0.1 mg/ml streptomycin,
and 0.25 .mu.g/ml of amphotericin B (all from Invitrogen Corp.,
Carlsbad, Calif.). The cells were grown on gelatin (from porcine
serum; Sigma, St. Louis, Mo.) coated tissue culture treated flasks
at 37.degree. C. and 5% CO.sub.2. Confluent cultures of HAEC's
between passage 4 and 8 were used in all studies.
NovoGel.TM. Mold
Preparation of 2% w/v NovoGel.TM. solution: 1 g of low melting
point NovoGel.TM. was dissolved in 50 ml of Dulbecco's phosphate
buffered saline (DPBS). Briefly, the DPBS and NovoGel.TM. were
heated to 85.degree. C. on a hot plate with constant stirring until
the NovoGel.TM. dissolved completely. NovoGel.TM. solution was
sterilized by steam sterilization at 125.degree. C. for 25 minutes.
The NovoGel.TM. solution remained in liquid phase as long as the
temperature is maintained above 66.5.degree. C. Below this
temperature a phase transition occurs, the viscosity of the
NovoGel.TM. solution increases and the NovoGel.TM. forms a solid
gel.
Preparation of NovoGel.TM. mold: A NovoGel.TM. mold was fabricated
for the incubation of cellular cylinders using a Teflon.RTM. mold
that fits a 10 cm Petri dish. Briefly, the Teflon.RTM. mold was
pre-sterilized using 70% ethanol solution and subjecting the mold
to UV light for 45 minutes. The sterilized mold was placed on top
of the 10 cm Petri dish (VWR International LLC, West Chester, Pa.)
and securely attached. This assembly (Teflon.RTM. mold+Petri dish)
was maintained vertically and 45 ml of pre-warmed, sterile 2%
NovoGel.TM. solution was poured in the space between the
Teflon.RTM. mold and the Petri dish. The assembly was then placed
horizontally at room temperature for 1 hour to allow complete
gelation of the NovoGel.TM. After gelation, the Teflon.RTM. print
was removed and the NovoGel.TM. mold was washed twice using DPBS.
17.5 ml of HASMC culture medium was then added to the NovoGel.TM.
mold.
HASMC-HAEC Cylinders
Fabrication of HASMC-HAEC mixed cellular cylinders: To prepare
mixed cellular cylinders HASMC and HAEC were individually collected
and then mixed at pre-determined ratios. Briefly, the culture
medium was removed from confluent culture flasks and the cells were
washed with DPBS (1 ml/5 cm.sup.2 of growth area). Cells were
detached from the surface of the culture flasks by incubation in
the presence of trypsin (1 ml/15 cm.sup.2 of growth area) for 10
minutes. HASMC were detached using 0.15% trypsin while HAEC were
detached using 0.1% trypsin. Following the incubation appropriate
culture medium was added to the flasks (2.times. volume with
respect to trypsin volume). The cell suspension was centrifuged at
200 g for 6 minutes followed by complete removal of supernatant
solution. Cell pellets were resuspended in respective culture
medium and counted using a hemacytometer. Appropriate volumes of
HASMC and HAEC were combined to yield mixed cell suspensions
containing 5, 7.5, 10, 12.5, and 15% HAEC (as a % of total cell
population). The mixed cell suspensions were centrifuged at 200 g
for 5 minutes followed by complete removal of supernatant solution.
Mixed cell pellets were resuspended in 6 ml of HASMC culture medium
and transferred to 20 ml glass vials, followed by incubation on an
orbital shaker at 150 rpm for 60 minutes, and at 37.degree. C. and
5% CO.sub.2. This allows the cells to aggregate with one another
and initiate cell-cell adhesions. Post-incubation, the cell
suspension was transferred to a 15 ml centrifuge tube and
centrifuged at 200 g for 5 minutes. After removal of the
supernatant medium, the cell pellet was resuspended in 400 .mu.l of
HASMC culture medium and pipetted up and down several times to
ensure all cell clusters were broken. The cell suspension was
transferred into a 0.5 ml microfuge tube placed inside a 15 ml
centrifuge tube followed by centrifugation at 2000 g for 4 minutes
to form a highly dense and compact cell pellet. The supernatant
medium was aspirated and the cells were transferred into capillary
tubes (OD 1.0 mm, ID 0.5 mm, L 75 mm; Drummond Scientific Co.,
Broomall, Pa.) by aspiration so as to yield cell cylinders 50 mm in
length. The cell paste inside the capillaries was incubated in
HASMC medium for 20 minutes at 37.degree. C. and 5% CO.sub.2. The
cellular cylinders were then deposited from the capillary tubes
into the grooves of the NovoGel.TM. mold (covered with HASMC
medium) using the plunger supplied with the capillaries. The
cellular cylinders were incubated for 24 and 48 hours at 37.degree.
C. and 5% CO.sub.2.
Example 2: Multi-Layered Vascular Tubes
Cell Culture
Smooth muscle cells: Primary human aortic smooth muscle cells
(HASMC; GIBCO) were maintained and expanded in low glucose
Dulbecco's modified eagle medium (DMEM) supplemented with 10% fetal
bovine serum (FBS), 100 U/ml Penicillin, 0.1 mg/ml streptomycin,
0.25 .mu.g/ml of amphotericin B, 0.01M of HEPES (all from
Invitrogen Corp., Carlsbad, Calif.), 50 mg/L of proline, 50 mg/L of
glycine, 20 mg/L of alanine, 50 mg/L of ascorbic acid, and 3
.mu.g/L of CuSO.sub.4 (all from Sigma, St. Louis, Mo.) at
37.degree. C. and 5% CO.sub.2. Confluent cultures of HASMC between
passage 4 and 8 were used in all studies.
Endothelial cells: Primary human aortic endothelial cells (HAEC)
were maintained and expanded in Medium 200 supplemented with 2%
FBS, 1 .mu.g/ml of hydrocortisone, 10 ng/ml of human epidermal
growth factor, 3 ng/ml of basic fibroblast growth factor, 10
.mu.g/ml of heparin, 100 U/ml Penicillin, 0.1 mg/ml streptomycin,
and 0.25 .mu.g/ml of amphotericin B (all from Invitrogen Corp.,
Carlsbad, Calif.). The cells were grown on gelatin (from porcine
serum) coated tissue culture treated flasks at 37.degree. C. and 5%
CO.sub.2. Confluent cultures of HAEC between passage 4 and 8 were
used in all studies.
Fibroblasts: Primary human dermal fibroblasts (HDF) were maintained
and expanded in Medium 106 supplemented with 2% FBS, 1 .mu.g/ml of
hydrocortisone, 10 ng/ml of human epidermal growth factor, 3 ng/ml
of basic fibroblast growth factor, 10 .mu.g/ml of heparin, 100 U/ml
Penicillin, and 0.1 mg/ml streptomycin (all from Invitrogen Corp.,
Carlsbad, Calif.) at 37.degree. C. and 5% CO.sub.2. Confluent
cultures of HDF between passage 4 and 8 were used in all studies.
NovoGel.TM. Solutions and Mold
Preparation of 2% and 4% (w/v) NovoGel.TM. solution: 1 g or 2 g
(for 2% or 4% respectively) of low melting point NovoGel.TM.
(Ultrapure LMP) was dissolved in 50 ml of Dulbecco's phosphate
buffered saline (DPBS). Briefly, the DPBS and NovoGel.TM. were
heated to 85.degree. C. on a hot plate with constant stirring until
the NovoGel.TM. dissolves completely. NovoGel.TM. solution was
sterilized by steam sterilization at 125.degree. C. for 25 minutes.
The NovoGel.TM. solution remains in liquid phase as long as the
temperature is maintained above 66.5.degree. C. Below this
temperature a phase transition occurs, the viscosity of the
NovoGel.TM. solution increases and the NovoGel.TM. forms a solid
gel.
Preparation of NovoGel.TM. mold: A NovoGel.TM. mold was fabricated
for the incubation of cellular cylinders using a Teflon.RTM. mold
that fit a 10 cm Petri dish. Briefly, the Teflon.RTM. mold was
pre-sterilized using 70% ethanol solution and subjecting the mold
to UV light for 45 minutes. The sterilized mold was placed on top
of the 10 cm Petri dish and securely attached. This assembly
(Teflon.RTM. mold+Petri dish) was maintained vertically and 45 ml
of pre-warmed, sterile 2% NovoGel.TM. solution was poured in the
space between the Teflon.RTM. mold and the Petri dish. The assembly
was then placed horizontally at room temperature for 1 hour to
allow complete gelation of the NovoGel.TM.. After gelation, the
Teflon.RTM. print was removed and the NovoGel.TM. mold was washed
twice using DPBS. Then, either 17.5 ml of HASMC culture medium was
added to the NovoGel.TM. mold for incubating HASMC-HAEC mixed cell
cylinders or 17.5 ml of HDF culture medium is added to the
NovoGel.TM. mold for incubating HDF cell cylinders.
Cellular Cylinders
Fabrication of HASMC-HAEC mixed cellular cylinders: To prepare
mixed cellular cylinders HASMC and HAEC were individually collected
and then mixed at pre-determined ratios. Briefly, the culture
medium was removed from confluent culture flasks and the cells were
washed with DPBS (1 ml/5 cm.sup.2 of growth area). Cells were
detached from the surface of the culture flasks by incubation in
the presence of trypsin (1 ml/15 cm.sup.2 of growth area) for 10
minutes. HASMC were detached using 0.15% trypsin while HAEC were
detached using 0.1% trypsin. Following the incubation appropriate
culture medium was added to the flasks (2.times. volume with
respect to trypsin volume). The cell suspension was centrifuged at
200 g for 6 minutes followed by complete removal of supernatant
solution. Cell pellets were resuspended in respective culture
medium and counted using a hemacytometer. Appropriate volumes of
HASMC and HAEC were combined to yield a mixed cell suspension
containing 15% HAEC and remainder 85% HASMC (as a percentage of
total cell population). The mixed cell suspension was centrifuged
at 200 g for 5 minutes followed by complete removal of supernatant
solution. Mixed cell pellets were resuspended in 6 ml of HASMC
culture medium and transferred to 20 ml glass vials, followed by
incubation on an orbital shaker at 150 rpm for 60 minutes, and at
37.degree. C. and 5% CO.sub.2. This allows the cells to aggregate
with one another and initiate cell-cell adhesions. Post-incubation,
the cell suspension was transferred to a 15 ml centrifuge tube and
centrifuged at 200 g for 5 mins. After removal of the supernatant
medium, the cell pellet was resuspended in 400 .mu.l of HASMC
culture medium and pipetted up and down several times to ensure all
cell clusters were broken. The cell suspension was transferred into
a 0.5 ml microfuge tube placed inside a 15 ml centrifuge tube
followed by centrifugation at 2000 g for 4 minutes to form a highly
dense and compact cell pellet. The supernatant medium was aspirated
and the cells were transferred into capillary tubes (OD 1.0 mm, ID
0.5 mm, L 75 mm) by aspiration so as to yield cell cylinders 50 mm
in length. The cell paste inside the capillaries was incubated in
HASMC medium for 20 minutes at 37.degree. C. and 5% CO.sub.2. The
cellular cylinders were then deposited from the capillary tubes
into the grooves of the NovoGel.TM. mold (covered with HASMC
medium) using the plunger supplied with the capillaries. The
cellular cylinders were incubated for 24 hours at 37.degree. C. and
5% CO.sub.2.
Fabrication of HDF cell cylinders: HDF cylinders were prepared
using a method similar to preparing HASMC-HAEC mixed cellular
cylinders. Briefly, the culture medium was removed from confluent
HDF culture flasks and the cells were washed with DPBS (1 ml/5
cm.sup.2 of growth area). Cells were detached from the surface of
the culture flasks by incubation in the presence of trypsin (0.1%;
1 ml/15 cm.sup.2 of growth area) for 10 minutes. Following the
incubation HDF culture medium was added to the flasks (2.times.
volume with respect to trypsin volume). The cell suspension was
centrifuged at 200 g for 6 minutes followed by complete removal of
supernatant solution. Cell pellets were resuspended in 6 ml of HDF
culture medium and transferred to 20 ml glass vials, followed by
incubation on an orbital shaker at 150 rpm for 75 minutes, and at
37.degree. C. and 5% CO.sub.2. Post-incubation, the cell suspension
was transferred to a 15 ml centrifuge tube and centrifuged at 200 g
for 5 minutes. After removal of the supernatant medium, the cell
pellet was resuspended in 400 .mu.l of HDF culture medium and
pipetted up and down several times to ensure all cell clusters were
broken. The cell suspension was transferred into a 0.5 ml microfuge
tube placed inside a 15 ml centrifuge tube followed by
centrifugation at 2000 g for 4 minutes to form a highly dense and
compact cell pellet. The supernatant medium was aspirated and the
cells were transferred into capillary tubes (OD 1.0 mm, ID 0.5 mm,
L 75 mm) by aspiration so as to yield cell cylinders 50 mm in
length. The cell paste inside the capillaries were incubated in HDF
culture medium for 20 minutes at 37.degree. C. and 5% CO.sub.2. The
cellular cylinders were then deposited from the capillary tubes
into the grooves of the NovoGel.TM. mold (covered with HDF medium).
The cellular cylinders were incubated for 24 hours at 37.degree. C.
and 5% CO.sub.2.
Fabrication of Multi-Layered Vascular Tubes
Preparation of NovoGel.TM. base plate: A NovoGel.TM. base plate was
fabricated by dispensing 10 ml of pre-warmed (>40.degree. C.)
NovoGel.TM. (2% w/v) into a 10 cm Petri dish. Immediately after
dispensing, the NovoGel.TM. was evenly spread so as to cover the
entire base of the dish and form a uniform layer. The Petri dish
was incubated at room temperature for 20 minutes to allow the
NovoGel.TM. to gel completely.
Multi-layered vascular tube: Vascular tubes consisting of an outer
layer of HDF and an inner layer of HASMC-HAEC were fabricated
utilizing HDF cylinders, and HASMC-HAEC mixed cell cylinders. A
geometrical arrangement as shown in FIG. 4 was utilized. Briefly,
at the end of the 24-hour incubation period mature HDF and
HASMC-HAEC cylinders were aspirated back into the capillary tubes
and placed in appropriate culture medium until further use. The
support structure consisting of NovoGel.TM. rods was prepared as
follows: Pre-warmed 2% NovoGel.TM. was aspirated into the capillary
tubes (L=50 mm) and rapidly cooled in cold PBS solution (4.degree.
C.). The 5 cm long gelled NovoGel.TM. cylinder was deposited from
the capillary (using the plunger) and laid down straight on the
NovoGel.TM. base plate. A second NovoGel.TM. cylinder was adjoined
to the first one and the process was repeated until 10 NovoGel.TM.
cylinders were deposited to form the first layer. At this point 20
.mu.l of PBS was dispensed above the NovoGel.TM. cylinders to keep
them wet. Further six NovoGel.TM. cylinders were deposited on top
of layer 1 at positions as shown in FIG. 4 (layer 2). Three HDF
cylinders were then deposited at positions 4, 5 and 6 to complete
layer 2. After dispensing each HDF cylinder 40 .mu.l of HDF culture
medium was dispensed on top of the deposited cylinder to assist the
deposition of the subsequent cylinder as well as to prevent
dehydration of the cellular cylinders. Next NovoGel.TM. cylinders
for layer 3 were deposited followed by HDF cylinders at positions 3
and 6. Following rewetting of the structure with HDF culture
medium, HASMC-HAEC mixed cylinders were laid down in positions 4
and 5. Subsequently, 40 .mu.l of HASMC medium and 40 .mu.l of HDF
medium were dispensed on top of the cell cylinders. Layer 4 was
completed by depositing NovoGel.TM. cylinders at positions 1 and 7,
HDF cylinders at positions 2 and 6, HASMC-HAEC mixed cylinders at
positions 3 and 5, and finally a 4% NovoGel.TM. cylinder at
position 4. Layers 5, 6 and 7 were completed similarly by laying
down NovoGel.TM. cylinders followed by HDF cylinders and finally
HASMC-HAEC cylinders at positions shown in FIG. 4. Once the entire
construct was completed 0.5 ml of warm NovoGel.TM. was dispensed
over each end of the construct and allowed to gel at room
temperature for 5 minutes. Following gelation of that NovoGel.TM.,
30 ml of HASMC medium was added to the Petri dish (to ensure the
entire construct was completely submerged). The construct was
incubated for 24 hours at 37.degree. C. and 5% CO.sub.2 to allow
for fusion between the cellular cylinders.
At the end of 24 hours, the surrounding NovoGel.TM. support
structure was removed from the fused multi-layered vascular
tube.
Example 3: Bioprinter
A bioprinter was assembled. The bioprinter contained a printer head
having a collet chuck grip for holding a cartridge, and a piston
for dispensing the contents of the cartridge. The cartridges used
were glass microcapillary tubes having a length of 75-85 mm. A new
capillary tube was loaded each time bio-ink or support material was
required.
In order to print structures, a dispense position repeatability of
.+-.20 .mu.m was required for the duration of the printing process,
i.e., when new capillaries were loaded into the printer head. In
order to maintain repeatability of all loaded capillary tubes
relative to the same point in the x-, y-, and z-directions, the
bioprinter contained a laser calibration system for calibrating the
position of the microcapillary tube. The laser calibration system
calibrated the position of all capillary tips to a common reference
location. All printing moves were made relative to this reference
position.
All three axes (x-, y-, and z-axes) were calibrated through usage
of a single laser distance measurement sensor. The system consisted
of a laser sensor and a laser beam. The sensor threshold was the
maximum sensing distance of the laser sensor. The sensor was
configured to ignore all signals further away than a pre-defined
threshold. The sensor used triangulation to determine distance to
the object (the capillary tip). The laser sensor was orientated
with the beam aimed vertically up (+z-axis).
Vertical Laser Calibration
For calibration in the x-axis: The capillary tip was moved in the
range of the laser sensor, with the tip to the left (-x) of the
laser beam. The capillary was moved to in the +x direction until
the sensor detected the capillary edge, and this position was
recorded. The above steps were repeated from the opposite side
(i.e., the tip was positioned at the right (+x) of the laser beam
and moved in the -x direction until the sensor detected the
capillary edge). The positions from both steps were averaged to
calculate the mid-point of the capillary. Optionally, the above
process was repeated for different y-positions and the calculated
mid-points were averaged.
For calibration in the y-axis: The above procedure (for the x-axis)
was repeated for the y-axis.
For calibration in the z-axis: The capillary tip was moved to above
the sensor beam so that the bean hit the bottom surface of the
capillary, and the tip was just outside of the sensor range
threshold. The capillary was lowered until the sensor threshold was
reached, and that position was recorded as the z-position.
Optionally, the above steps were repeated at multiple points on the
capillary tip surface and measured heights were averaged.
Horizontal Laser Calibration
For calibration in the y-axis: The capillary was moved so that the
tip was just below the laser beam height, and the capillary was off
to one side (in the y-direction). The capillary was moved in the
y-direction towards the laser. The capillary was stopped when the
laser sensor detected the beam reflected off the capillary, and
this position was recorded. The above steps were repeated with the
capillary off to the other side of the laser, and moved in the -y
direction). The mid-point from the above steps was recorded as the
y-position.
For calibration in the x-axis: Using the results of the calibration
in the y-axis, the y-axis was moved so that the laser was centered
on the capillary. The capillary was moved past the sensor threshold
and moved towards the sensor. The capillary was stopped as soon as
the capillary crossed the sensor threshold and the sensor output
changed. This position, plus 1/2 the capillary width (from the
y-calibration) was recorded as the x-position.
For calibration in the z-axis: The capillary was moved up from the
x-position until it was clear of the laser beam. The capillary tip
was moved down towards the laser beam, and stopped as soon as the
laser beam was interrupted (using the same process as for the
y-axis). This position was recorded as the z-position.
Capillary Priming
Before printing from a capillary, the bio-ink or support material
inside the capillary was primed so that the bio-ink or support
material would begin printing at the very tip of the capillary. The
calibration laser was used to prime the capillary. The capillary
tip was moved just above the laser beam, with the beam centered in
the y-axis. The tip was between 20-100 .mu.m above the laser beam.
The dispensing piston in the printer head was driven down until the
bio-ink or support material started to dispense out of the
capillary tip and interrupted the laser beam. The dispensed bio-ink
or support material was aspirated back into the capillary tube by
driving the piston in the reverse direction (20-100 .mu.m). The
capillary was then primed and ready to dispense.
NovoGel.TM. Capillary Cleaning
NovoGel.TM. was used as a support material. In order to remove
excess NovoGel.TM. sticking to the outside surface of the capillary
tube and to avoid the excess NovoGel.TM. from affecting print
quality, the excess NovoGel.TM. was removed. A wiping feature was
integrated into a bulk NovoGel.TM. vessel. A bulk NovoGel.TM.
vessel was fitted with a standard medical vial with an open cap for
a septum to be attached. A septum was configured with a cross cut
in the center of 1-2 mm thick silicone. By dipping the capillary
into the bulk NovoGel.TM. vessel through the septum and aspirating
NovoGel.TM., excess NovoGel.TM. was wiped from the capillary as it
exited the vessel, and remained in the bulk vessel.
Printing of a Vascular Structure
The bioprinter and cartridge was assembled as above. The bioprinter
had a stage having a Petri dish for receiving structures generated
by the bioprinter. The Petri dish was coated with NovoGel.TM..
A two dimensional representation (see e.g., FIG. 4) of a vascular
structure was inputted by a user into a software program into a
computer which was connected to the bioprinter. The two dimensional
representation of the vascular structure consisted of rods of
HASMC-HAEC mixed cellular cylinders, HDF cylinders, and NovoGel.TM.
rods defining the voids of the vascular structure and surrounding
the vascular structure. HASMC-HAEC mixed cellular cylinders and HDF
cellular cylinders were prepared as in Example 1, and aspirated
into capillary tubes for insertion into the collet chuck of the
printer head. Alternatively, capillary tubes were loaded into the
printer head and dipped into the bulk NovoGel.TM. vessel and
NovoGel.TM. was aspirated into the capillary tube. The capillary
tubes were calibrated using the vertical laser calibration
system.
When the commands from the software program were provided to the
bioprinter, the bioprinter would print the three-dimensional
structure, alternating between HASMC-HAEC rods, HDF rods and
NovoGel.TM. rods, onto the Petri dish, in predetermined locations.
See Example 2. After each rod was laid down on the Petri dish, the
rod was wetted with a small amount of culture medium. Once the
entire construct was completed warm NovoGel.TM. was dispensed over
each end of the construct and allowed to gel at room temperature,
and cell culture medium was added to the Petri dish to submerge the
entire construct. The construct was then incubated at 37.degree. C.
and 5% CO.sub.2 to allow for fusion between the cellular cylinders.
At the end of the incubation time, the surrounding NovoGel.TM.
support structure was removed from the fused multi-layered vascular
tube.
While the invention has been described in connection with specific
embodiments thereof, it will be understood that the inventive
methodology is capable of further modifications. This patent
application is intended to cover any variations, uses, or
adaptations of the invention following, in general, the principles
of the invention and including such departures from the present
disclosure as come within known or customary practice within the
art to which the invention pertains and as may be applied to the
essential features herein before set forth and as follows in scope
of the appended claims.
* * * * *
References